Radiographic image capturing apparatus and radiographic image capturing system

ABSTRACT

A radiographic image capturing apparatus has a radiation source device including a radiation source, and a detector device including a radiation detector. At least one of the radiation source device and the detector device includes an electric power supply limiting unit for limiting supply of electric power. The electric power supply limiting unit has an activator/deactivator for determining activation or deactivation of supply of electric power between the radiation source device and the detector device, based on a present position of a corresponding one of the radiation source device and the detector device, or based on distance between the radiation source device and the detector device, and an electric power supply activator for enabling supply of electric power between the radiation source device and the detector device, if the activator/deactivator determines activation of supply of electric power between the radiation source device and the detector device.

CROSS-REFERENCE TO RELATED APPLICATION

This application is based upon and claims the benefit of priority fromJapanese Patent Applications No. 2010-019635 filed on Jan. 29, 2010, No.2010-030543 filed on Feb. 15, 2010, No. 2010-037586 filed on Feb. 23,2010, No. 2010-275185 filed on Dec. 10, 2010, No. 2010-275187 filed onDec. 10, 2010 and No. 2010-275188 filed on Dec. 10, 2010, of which thecontents are incorporated herein by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to a radiographic image capturingapparatus and a radiographic image capturing system. More particularly,the present invention concerns a radiographic image capturing apparatuspreferably for use as a portable radiographic image capturing apparatus,which can be carried outdoors by an operator, and a radiographic imagecapturing system.

2. Description of the Related Art

In the medical field, there have widely been used radiographic imagecapturing apparatus, which apply radiation to a subject and guideradiation that has passed through the subject to a radiation conversionpanel (radiation detector), which captures a radiographic image fromsuch radiation. Known forms of radiation conversion panels includeconventional radiation film for recording a radiographic image by way ofexposure, and stimulable phosphor panels for storing radiation energyrepresenting a radiographic image in a phosphor, and reproducing theradiographic image as stimulated light by applying stimulating light tothe phosphor. Radiation film with the recorded radiographic image issupplied to a developing device to develop the radiographic image, orthe stimulable phosphor panel is supplied to a reading device to readthe radiographic image as a visible image.

In an operating room or the like, for the purpose of quickly andappropriately treating patients, it is necessary to read a recordedradiographic image immediately from a radiation conversion panel afterthe radiographic image has been captured. As a radiation detector whichmeets such a requirement, there have been developed a radiation detectorof a direct conversion type (electronic cassette) having a solid-statedetector for converting radiation directly into electric signals, and aradiation detector of an indirect conversion type (electronic cassette)having a scintillator for temporarily converting radiation into visiblelight and a solid-state detector for converting such visible light intoelectric signals (see U.S. Pat. No. 5,514,873).

Such radiographic image capturing apparatus are developed on theassumption that they will be used to capture radiographic images ofpatients in medical organizations.

There are potential demands for capturing radiographic images outside ofmedical organizations. To meet such demands, radiographic imagecapturing apparatus, which are mounted on motor vehicles used to performmedical checkups, have been proposed in the art. However, such proposedradiographic image capturing apparatus, which are disposed on medicalcheckup motor vehicles, are relatively large in size. Needs have arisenfor capturing radiographic images of persons who suffer from naturaldisasters at disaster sites, or persons who are receiving home-careservices at their homes. However, existing medical checkup motorvehicles cannot be used in the former applications, since it isdifficult to get to disaster sites. Although existing medical checkupmotor vehicles may be driven to the homes of persons who are receivinghome-care services, the image capturing process is highly burdensome topeople to be imaged, because they have to be taken from their homes intothe medical checkup motor vehicle in order to capture radiographicimages of such people. Therefore, there have been demands for small-sizeportable radiographic image capturing apparatus for use at naturaldisaster sites or at homes receiving home-care services.

There has been developed a portable radiographic image capturingapparatus, which can be folded into a compact form in its entirety (seeJapanese Laid-Open Patent Publication No. 2007-530979 (PCT)). Inaddition, radiation sources comprising field-electron-emission-typeelectron sources based on carbon nanotube (CNT) technology have alsobeen developed (see Japanese Laid-Open Patent Publication No.2007-103016, and AIST: Press Release, “Development of Portable X-raySources Using Carbon Nanostructures” [online], Mar. 19, 2009, NationalInstitute of Advanced Industrial Science and Technology, Internet<URL:http://www.aist.go.jp/aistj/press_release/pr2009/pr20090319/pr20090319.html>(hereinafter referred to as “Document 1”). It is expected thatsmall-size, lightweight radiographic image capturing apparatus includingradiation sources will become available in the art. Further, a portablesize and high energy X-ray source was developed by using LiTaO₃ that isa typical pyroelectric crystal (see “Applying Pyroelectric Crystal toSmall High Energy X-Ray Source”, Advances in X-Ray Chemical Analysis,Japan, 41, 2010, pages 195-200 (hereinafter referred to as “Document2”)).

Wireless electric power transmitting schemes are known from IEDM PlenaryTalk, “Arrival of Contactless Power Transmission Sheet Expected to beEmbedded in Walls and Floors, developed by the University of Tokyo”[online], Dec. 4, 2006, Internet<URL:http://techon.nikkeibp.co.jp/article/NEWS/20061204/124943/>(hereinafter referred to as “Document 3”), and Nikkei Electronics,“Development of Wireless Power Transmission Technology, a 60-W LampTurned on in Experiment,” Dec. 3, 2007, pages 117-128 (hereinafterreferred to as “Document 4”). The process disclosed in Document 3transmits electric power based on electromagnetic induction from aprimary coil embedded in a contactless power transmission sheet. Theprocess disclosed in Document 4 is a wireless power transmissiontechnology based on magnetic field resonance between two LC resonators.

If a small-size radiation source can be reduced in size as disclosed inJapanese Laid-Open Patent Publication No. 2007-530979 (PCT), JapaneseLaid-Open Patent Publication No. 2007-103016, Document 1, and Document2, then the radiation source may be combined with an electronic cassetteas disclosed in U.S. Pat. No. 5,514,873 in order to reduce the size andweight of the radiographic image capturing apparatus, which includes aradiation source and an electronic cassette, thereby allowing theradiographic image capturing apparatus to be moved with ease. In otherwords, a portable radiographic image capturing apparatus can berealized.

However, since such a portable radiographic image capturing apparatusmainly is used outdoors, a problem arises as to the availability of apower supply therefor. One solution would be to carry separate batteriestogether with the portable radiographic image capturing apparatus. Morespecifically, it is necessary to prepare a battery dedicated for theradiation source, a battery dedicated for the electronic cassette, and abattery dedicated for a controller (personal computer), etc., for usewith the portable radiographic image capturing apparatus. In addition tosuch batteries, backup batteries also need to be carried, in case imageshave to be recaptured or additional images have to be captured. As aresult, the entire radiographic image capturing system to be carriedaround is liable to be of an increased size and weight, thus reducingthe ease (including portability) with which the radiographic imagecapturing system can be used.

SUMMARY OF THE INVENTION

An object of the present invention is to provide a radiographic imagecapturing apparatus and a radiographic image capturing system, which arecapable of supplying electric power to a radiation source and aradiation detector even outdoors, reducing consumption of electricpower, and minimizing the number batteries used therein, which can beused easily and efficiently both inside and outside of places such asmedical organizations, accident sites, disaster sites, medical checkupsites, home-care service sites, etc., which can reduce consumption ofelectric power by separately storing and carrying the radiation sourceand the radiation detector, and which can prevent the radiation sourceand the radiation detector from being stolen as a set.

According to an aspect of the present invention, there is provided aradiographic image capturing apparatus comprising a radiation sourcedevice including a radiation source for outputting radiation, and adetector device including a radiation detector for detecting radiationthat is transmitted through a subject when the subject is irradiatedwith radiation by the radiation source, and converting the detectedradiation into a radiographic image, at least one of the radiationsource device and the detector device having an electric power supplylimiting unit for limiting supply of electric power, the electric powersupply limiting unit comprising an activator/deactivator for determiningactivation or deactivation of supply of electric power between theradiation source device and the detector device, based on a presentposition of a corresponding one of the radiation source device and thedetector device, or based on a distance between the radiation sourcedevice and the detector device, and an electric power supply activatorfor enabling supply of electric power between the radiation sourcedevice and the detector device, if the activator/deactivator determinesactivation of supply of electric power between the radiation sourcedevice and the detector device.

In the radiographic image capturing apparatus, the activator/deactivatorcomprises a present position acquirer for acquiring the present positionof the corresponding one of the radiation source device and the detectordevice, and a determiner for determining whether or not the acquiredpresent position is outside of a medical organization, and the electricpower supply activator enables supply of electric power between theradiation source device and the detector device, if the determinerjudges that the acquired present position is outside of the medicalorganization.

In the radiographic image capturing apparatus, the activator/deactivatorcomprises a present position acquirer for acquiring the present positionof the corresponding one of the radiation source device and the detectordevice, and a determiner for determining whether or not the acquiredpresent position is in a preset location, and the electric power supplyactivator enables supply of electric power between the radiation sourcedevice and the detector device, if the determiner judges that theacquired present position is in the preset location.

In the radiographic image capturing apparatus, the activator/deactivatorcomprises a determiner for determining whether or not the distancebetween the radiation source device and the detector device satisfies acertain condition, and the electric power supply activator enablessupply of electric power between the radiation source device and thedetector device, if the determiner judges that the distance satisfiesthe certain condition.

According to another aspect of the present invention, there is alsoprovided a radiographic image capturing system comprising a radiationsource device including a radiation source for outputting radiation, adetector device including a radiation detector for detecting radiationthat is transmitted through a subject when the subject is irradiatedwith radiation by the radiation source, and converting the detectedradiation into a radiographic image, an activator/deactivator fordetermining activation or deactivation of supply of electric powerbetween the radiation source device and the detector device, based on apresent position of at least one of the radiation source device and thedetector device, or based on a distance between the radiation sourcedevice and the detector device, and an electric power supply activatorfor enabling supply of electric power between the radiation sourcedevice and the detector device, if the activator/deactivator determinesactivation of supply of electric power between the radiation sourcedevice and the detector device.

In the radiographic image capturing system, the activator/deactivatorcomprises a present position acquirer for acquiring the present positionof at least one of the radiation source device and the detector device,and a determiner for determining whether or not the acquired presentposition is outside of a medical organization, and the electric powersupply activator enables supply of electric power between the radiationsource device and the detector device, if the determiner judges that theacquired present position is outside of the medical organization.

In the radiographic image capturing system, the activator/deactivatorcomprises a present position acquirer for acquiring the present positionof at least one of the radiation source device and the detector device,and a determiner for determining whether or not the acquired presentposition is in a preset location, and the electric power supplyactivator enables supply of electric power between the radiation sourcedevice and the detector device, if the determiner judges that theacquired present position is in the preset location.

In the radiographic image capturing system, the activator/deactivatorcomprises a determiner for determining whether or not the distancebetween the radiation source device and the detector device satisfies acertain condition, and the electric power supply activator enablessupply of electric power between the radiation source device and thedetector device, if the determiner judges that the distance satisfiesthe certain condition.

According to the present invention, the radiation source and theradiation detector can be supplied with electric power even if theradiographic image capturing apparatus is used outdoors. Batteries thatneed to be included in the radiographic image capturing apparatus areminimized. Therefore, the radiographic image capturing apparatus isconvenient for use outside of a medical organization, or in a presetlocation such as a medical organization, or in any of various othersites including an accident site, a disaster site, a medical checkupsite, a home-care service site, etc. The radiation source and theradiation detector can separately be stored and carried for reducedelectric power consumption, as well as for protection against beingstolen as a set.

The above and other objects, features, and advantages of the presentinvention will become more apparent from the following description whentaken in conjunction with the accompanying drawings in which preferredembodiments of the present invention are shown by way of illustrativeexample.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a radiographic image capturing apparatus(first radiographic image capturing apparatus) according to a firstembodiment of the present invention;

FIG. 2 is a perspective view showing the manner in which the firstradiographic image capturing apparatus is carried;

FIG. 3 is a horizontal cross-sectional view taken along line of FIG. 1;

FIG. 4 is a cross-sectional view of the first radiographic imagecapturing apparatus, showing a radiation source device separated from acassette;

FIG. 5 is a cross-sectional view, shown partially in block form, ofinternal details of the radiation source device shown in FIG. 1;

FIG. 6 is an elevational view, partially in cross section, showing themanner in which the first radiographic image capturing apparatuscaptures a radiographic image;

FIG. 7 is an elevational view showing the manner in which the firstradiographic image capturing apparatus is readied to captureradiographic images;

FIG. 8 is an elevational view showing the manner in which the firstradiographic image capturing apparatus captures a radiographic image;

FIG. 9 is a schematic view showing a pixel array of a radiation detectorof the first radiographic image capturing apparatus;

FIG. 10 is a block diagram of a circuit arrangement of the radiationdetector disposed in the cassette;

FIG. 11 is a block diagram of the first radiographic image capturingapparatus;

FIG. 12 is a perspective view of a mobile terminal, which displays aradiographic image on a display unit thereof;

FIG. 13 is a block diagram of a battery unit;

FIG. 14 is a block diagram of a battery controller;

FIG. 15A is a block diagram of a first activator/deactivator accordingto a first mode;

FIG. 15B is a block diagram of a first activator/deactivator accordingto a second mode;

FIG. 16A is a block diagram of a second activator/deactivator accordingto a first mode;

FIG. 16B is a block diagram of a fourth activator/deactivator;

FIG. 17A is a block diagram of a third activator/deactivator accordingto a first mode;

FIG. 17B is a block diagram of a third activator/deactivator accordingto a second mode;

FIG. 17C is a block diagram of a third activator/deactivator accordingto a third mode;

FIG. 18 is a block diagram of a power controller according to a firstspecific example;

FIG. 19 is a block diagram of a power controller (including a powermanager) according to a second specific example;

FIG. 20 is a block diagram of a cassette selection activator and acassette selector;

FIG. 21 is a block diagram of an integrated supply activator and anintegrated supply;

FIG. 22 is a block diagram of a power manager;

FIG. 23 is a first flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions, which are free of timing controls;

FIG. 24 is a second flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions, which are free of timing controls;

FIG. 25 is a first flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions for supplying electric power before capturing of radiographicimages;

FIG. 26 is a second flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions for supplying electric power before capturing of radiographicimages;

FIG. 27 is a third flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions for supplying electric power before capturing of radiographicimages;

FIG. 28 is a first flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions for supplying electric power after capturing of radiographicimages;

FIG. 29 is a second flowchart of an operation sequence of the firstradiographic image capturing apparatus, operated under supply timingconditions for supplying electric power after capturing of radiographicimages;

FIG. 30 is a perspective view of a modification of the firstradiographic image capturing apparatus;

FIG. 31 is a perspective view of another modification of the firstradiographic image capturing apparatus;

FIG. 32 is a perspective view of still another modification of the firstradiographic image capturing apparatus;

FIG. 33 is a perspective view of a radiographic image capturingapparatus (second radiographic image capturing apparatus) according to asecond embodiment of the present invention;

FIG. 34 is a perspective view showing the manner in which the secondradiographic image capturing apparatus is carried;

FIG. 35 is a horizontal cross-sectional view taken along line XXXV-XXXVof FIG. 33;

FIG. 36 is a plan view of the second radiographic image capturingapparatus, showing a radiation source device separated from a cassetteshown in FIG. 33;

FIG. 37 is a cross-sectional view showing the manner in which the secondradiographic image capturing apparatus captures a radiographic image;

FIG. 38 is a view showing in greater detail a source-to-image distance(SID) that is illustrated in FIG. 37;

FIG. 39 is a perspective view showing the manner in which the secondradiographic image capturing apparatus is readied to captureradiographic images;

FIG. 40 is a perspective view showing the manner in which the secondradiographic image capturing apparatus captures a radiographic image;

FIG. 41 is a perspective view of a radiographic image capturingapparatus (third radiographic image capturing apparatus) according to athird embodiment of the present invention;

FIG. 42 is a perspective view of the third radiographic image capturingapparatus;

FIG. 43 is a side elevational view of the third radiographic imagecapturing apparatus;

FIG. 44 is a perspective view showing the manner in which the thirdradiographic image capturing apparatus is carried;

FIG. 45 is a block diagram of a portion of a PC (Personal Computer),which is used with the third radiographic image capturing apparatus;

FIG. 46 is a block diagram of an electric power collector of the thirdradiographic image capturing apparatus;

FIG. 47 is a flowchart of an operation sequence of the power collectorshown in FIG. 46;

FIG. 48 is a cross-sectional view schematically illustrating thestructure of three pixel units of a radiation detector according to amodified example of the invention; and

FIG. 49 is a view schematically illustrating the structure of a TFT anda charge storage unit shown in FIG. 48.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Like or corresponding parts are denoted by like or correspondingreference characters throughout the views.

As shown in FIGS. 1 and 2, a radiographic image capturing apparatus 10Aaccording to a first embodiment of the present invention, whichhereinafter will be referred to as a “first radiographic image capturingapparatus 10A,” includes a cassette (detector device) 12 having asubstantially rectangular outer contour shaped as a housing, and whichis made of a material permeable to radiation 46 (see FIG. 5), and acylindrical radiation source device 18 held in the cassette 12 by a pairof holders 16 a, 16 b, which project outwardly from opposite ends of oneside 14 a of the cassette 12.

The cassette 12 has crisscross guide lines 22 disposed on a surface(irradiated surface) 20 thereof, which serve as a reference for an imagecapturing area and an image capturing position. The cassette 12 also hasa grip 24 on another side 14 b thereof remote from the one side 14 a.The cassette 12 has two other sides 14 c, 14 d extending perpendicularto and between the sides 14 a, 14 b, which are opposite to each other.On the side 14 c, there are disposed a USB (Universal Serial Bus)terminal 28 as an interface means for sending information to andreceiving information from an external device, a card slot 32 forinsertion of a memory card 30 therein, and an unlocking button 34 to bedescribed later. The side 14 c also supports thereon a mobile terminal42, which is detachable from the cassette 12. The mobile terminal 42includes a display unit 36 and an operating unit 40 having a number ofcontrol buttons operable by a doctor or radiological technician(hereinafter referred to as an “operator”) 38 who handles the firstradiographic image capturing apparatus 10A. The radiation source device18 has an exposure switch 48, which can be operated by the operator 38in order to cause a radiation source 44 (see FIG. 5), which shall bedescried later, to start emitting radiation 46.

FIGS. 1 and 2 show the first radiographic image capturing apparatus 10A,which is carried by the operator 38. When the first radiographic imagecapturing apparatus 10A is carried, the radiation source device 18 andthe cassette 12 are integrally joined to each other. The operator 38grips the grip 24 and carries the first radiographic image capturingapparatus 10A to a desired site, such as an accident site, a disastersite, a medical checkup site, or a home receiving home-care servicesoutside of a medical organization, or somewhere inside of a medicalorganization. When the operator 38 arrives at the site, the operator 38operates the first radiographic image capturing apparatus 10A in orderto capture radiographic images of a victim at the accident site or thedisaster site, or an examinee at the medical checkup site, or a personreceiving home-care services at home. The victim or person whoseradiographic images are to be captured will hereinafter be referred toas a “subject” 50 (see FIG. 6).

When the radiation source device 18 and the cassette 12 are joined toeach other integrally, they are secured together by a joining mechanism82 (see FIG. 3), to be described later, so that the first radiographicimage capturing apparatus 10A can be carried by the operator 38. Theradiation source device 18 can be detached from the cassette 12. If theradiation source device 18 includes a locking mechanism for locking atape measure 72 (see FIGS. 4 and 11) as it is unreeled, then theradiation source device 18 can be detached from the cassette 12 whilethe tape measure 72 is unlocked from the locking mechanism. With theradiation source device 18 mounted on the cassette 12, a radiographicimage of the subject 50 can be captured using another radiation sourcedevice 18. In such a case, the first radiographic image capturingapparatus 10A is constituted by the cassette 12, on which the radiationsource device 18 is mounted, and the other radiation source device 18.These components are managed by a data center at a time when imagecapturing conditions are entered and established. The cassette 12 andthe radiation source device 18 can thus be managed separately from eachother.

The portable first radiographic image capturing apparatus 10A, which hasbeen brought to a site such as an accident site or a disaster siteoutside of a medical organization, or to a preset disaster site or apreset home receiving home-care services, will be described below withreference to FIGS. 3 through 8.

As shown in FIG. 3, the sides 14 a, 14 b, 14 c, 14 d of the cassette 12are constituted by respective side walls 52 a, 52 b, 52 c, 52 d. The USBterminal 28, the card slot 32, and the unlocking button 34 are providedon the side wall 52 c. The side wall 52 c has a recess 54, which isdefined between the card slot 32 and the unlocking button 34. The mobileterminal 42 (see FIG. 2) can be placed in the recess 54.

When the unlocking button 34 is pressed by the operator 38 (see FIG. 2),the unlocking button 34 is displaced along the side wall 52 a toward theside wall 52 d. A slide 56 projects along the side wall 52 a from asurface of the unlocking button 34 that faces the side wall 52 d, and aspring 60 acts between the slide 56 and a tooth 58 that projectsinwardly from the side wall 52 a. The spring 60 normally biases theunlocking button 34 to move in a direction from the tooth 58 toward theside wall 52 c. The side wall 52 a has a through hole 62 defined in aportion thereof against which the slide 56 slides, the through hole 62extending from an inner surface of the side wall 52 a to an outersurface thereof. The slide 56 has a hook 64, which extends through thethrough hole 62.

As shown in FIGS. 3 and 4, the radiation source device 18 has a throughhole 66 defined therein at a location aligned with the through hole 62of the cassette 12 when the radiation source device 18 is held in thecassette 12 by the holders 16 a, 16 b. The through hole 66 is ofsubstantially the same size as the through hole 62. When the hook 64 isdisplaced toward the side wall 52 c under the bias of the spring 60, thehook 64 engages with an edge of the through hole 66 and locks theradiation source device 18 in place, thereby integrally joining theradiation source device 18 to the cassette 12 (see FIG. 3).

The radiation source device 18 has an electrically conductive connectionterminal (first radiation source connection terminal) 68 a mounted on anend thereof that faces the holder 16 a, and also has an electricallyconductive connection terminal (second radiation source connectionterminal) 68 b mounted on another end thereof that faces the holder 16b. The first connection terminal 68 a is convex in shape toward theholder 16 a, whereas the second connection terminal 68 b is concave inshape toward the holder 16 b. The radiation source device 18 has a firstenergy input/output unit 300, or a second energy input/output unit 302(see FIG. 13) for inputting and outputting electric power through awired or wireless link, for example. The first radiation sourceconnection terminal 68 a and the second radiation source connectionterminal 68 b, for example, constitute the first energy input/outputunit 300 or the second energy input/output unit 302, respectively, andmay be electrically connected through a wireless link. The first energyinput/output unit 300 or the second energy input/output unit 302 ismounted on a side wall of the radiation source device 18 (see FIG. 1).

The holder 16 a of the cassette 12 has an electrically conductiveconnection terminal (first cassette connection terminal) 70 a on asurface thereof that faces the radiation source device 18. The holder 16b of the cassette 12 has an electrically conductive connection terminal(second cassette connection terminal) 70 b on a surface thereof thatfaces the radiation source device 18. The first connection terminal 70 ais concave, complementary in shape to the first convex connectionterminal 68 a, whereas the second connection terminal 70 b is convex,complementary in shape to the concave second connection terminal 68 b.The cassette 12 has a first energy input/output unit 300 or a secondenergy input/output unit 302 (see FIG. 13) for inputting and outputtingelectric power through a wired or wireless link, for example. The firstcassette connection terminal 70 a and the second cassette connectionterminal 70 b, for example, constitute the first energy input/outputunit 300 or the second energy input/output unit 302, and may beelectrically connected through a wireless link. The first energyinput/output unit 300 or the second energy input/output unit 302 ismounted on the side 14 c of the cassette 12.

As shown in FIG. 3, when the hook 64 engages the edge of the throughhole 66 under the resiliency of the spring 60 in order to keep theradiation source device 18 and the cassette 12 joined integrally witheach other, the convex first connection terminal 68 a and the concavefirst connection terminal 70 a engage with each other, and the concavesecond connection terminal 68 b and the convex second connectionterminal 70 b engage with each other, respectively. Therefore, theradiation source device 18 and the cassette 12 are securely andintegrally joined with each other. Consequently, the connectionterminals 68 a, 68 b, 70 a, 70 b function as members for assisting thehook 64 and the through hole 66 in maintaining the radiation sourcedevice 18 and the cassette 12 in an integrally joined condition.

As shown in FIG. 4, when the operator 38 presses the unlocking button 34to move the unlocking button 34 toward the side wall 52 d against theresiliency of the spring 60, the hook 64 and the slide 56 are displacedtoward the side wall 52 d, so as to bring the hook 64 out of engagementwith the edge of the through hole 66. While the hook 64 is kept out ofengagement with the edge of the through hole 66, i.e., while theoperator 38 presses the unlocking button 34, the operator 38 can removeor separate the radiation source device 18 from the cassette 12, wherebythe radiation source device 18 and the cassette 12 are released fromeach other.

The cassette 12 houses therein a tape measure 72 comprising a ribbon 76marked with graduations 74, which is coiled into a roll by a spring, notshown, in the tape measure 72. The tape measure 72 is combined with arotary encoder 78 on one side thereof, for detecting the length by whichthe ribbon 76 is reeled out from the tape measure 72. The ribbon 76,which is reeled out from the tape measure 72, extends through a hole 80that is defined in the side wall 52 a at a location facing the tapemeasure 72, and a distal end of the ribbon 76 is fixed to the radiationsource device 18 near the second connection terminal 68 b.

When the radiation source device 18 and the cassette 12 are joinedintegrally with each other as shown in FIG. 3, most of the ribbon 76 iscoiled into a roll inside the tape measure 72 under the resiliency ofthe spring. On the other hand, when the radiation source device 18 andthe cassette 12 are not joined integrally with each other, as shown inFIGS. 4 through 8, the ribbon 76 can be pulled out of the tape measure72 through the hole 80 by separating the radiation source device 18 awayfrom the cassette 12 against the resiliency of the spring.

The unlocking button 34, the slide 56, the spring 60, the hook 64, theconnection terminals 68 a, 68 b, 70 a, 70 b, and the tape measure 72jointly make up a joining mechanism 82 for integrally joining theradiation source device 18 and the cassette 12 with each other when thefirst radiographic image capturing apparatus 10A is carried, and alsofor enabling the radiation source device 18 and the cassette 12 to beseparated from each other when the first radiographic image capturingapparatus 10A is utilized to capture radiographic images.

The tape measure 72 comprises the ribbon 76, which is marked withgraduations 74 in the illustrated embodiment. However, as a functionalequivalent to the ribbon 76, the tape measure 72 may comprise a stringmarked with graduations 74.

As shown in FIGS. 3 and 6, the cassette 12 also houses therein a grid 84for removing scattered rays of radiation 46 from the subject 50 when theradiation source 44 applies radiation 46 with respect to the subject 50,a radiation detector 86 for detecting radiation 46 that has passedthrough the subject 50, and a lead plate 88 for absorbing back scatteredrays of radiation 46, which are successively arranged in this order fromthe irradiated surface 20 of the cassette 12. The irradiated surface 20of the cassette 12 may also be constructed as the grid 84.

The radiation detector 86 may comprise a radiation detector (including afront surface reading type and a rear surface reading type) of anindirect conversion type, including a scintillator for convertingradiation 46 that has passed through the subject 50 into visible light,and solid-state detectors (hereinafter also referred to as pixels) madeof amorphous silicon (a-Si) or the like for converting the visible lightinto electric signals. A radiation detector of ISS (Irradiation SideSampling) type as a front surface reading type, comprises solid-statedetectors and a scintillator that are successively provided along anirradiation direction of the radiation 46. A radiation detector of PSS(Penetration Side Sampling) type as a rear surface reading type,comprises a scintillator and solid-state detectors that are successivelyprovided along the irradiation direction of the radiation 46. As well asthe above-described indirect conversion type, the radiation detector 86may also comprise a radiation detector of a direct conversion type,comprising solid-state detectors made of amorphous selenium (a-Se) orthe like for converting a dose of radiation 46 directly into electricsignals.

As shown in FIG. 3, the cassette 12 also houses therein a battery unit304 as a power supply for the cassette 12, a battery controller(electric power supply limiting unit) 306 for limiting and controllingsupply of electric power to the battery unit 304, a cassette controller92 for controlling the radiation detector 86 (see FIG. 6) with electricpower supplied from the battery unit 304, and a transceiver 94 forsending and receiving signals including information concerning radiation46 that is detected by the radiation detector 86, to and from anexternal circuit. A plate of lead or the like should preferably beplaced over the side surfaces of the cassette controller 92 and thetransceiver 94 under the irradiated surface 20 in order to protect thecassette controller 92 and the transceiver 94 against damage, whichwould otherwise be caused if the cassette controller 92 and thetransceiver 94 were irradiated with radiation 46.

The battery unit 304 supplies electric power to the rotary encoder 78,the radiation detector 86, the cassette controller 92, and thetransceiver 94 in the cassette 12. The battery unit 304 can also chargethe mobile terminal 42 when the mobile terminal 42 is placed in therecess 54. As shown in FIG. 13, the battery unit 304 includes, inaddition to the first energy input/output unit 300 and the second energyinput/output unit 302, a battery (electric power storage unit) 308, afirst energy converter 310, and a second energy converter 312. Thebattery unit 304 can be supplied with (i.e., charged by) electric powerfrom an external circuit, or can supply electric power to an externalcircuit, over a wired or wireless link via the first energy input/outputunit 300 and/or the second energy input/output unit 302. A firstswitcher 314 a is connected between the first energy input/output unit300 and the first energy converter 310. A second switcher 314 b isconnected between the second energy input/output unit 302 and the secondenergy converter 312. Third through fifth switchers 314 c through 314 eare connected between the battery 308 and the first energy input/outputunit 300 and the second energy input/output unit 302.

The first energy converter 310 comprises a first input converter 316 anda first output converter 318. The second energy converter 312 comprisesa second input converter 320 and a second output converter 322. Forinputting electric power via the first energy input/output unit 300, thefirst switcher 314 a electrically connects the first energy input/outputunit 300 and the first input converter 316 to each other, while thethird switcher 314 c and the fifth switcher 314 e electrically connectthe first input converter 316 and the battery 308 to each other.Conversely, for outputting electric power via the first energyinput/output unit 300, the first switcher 314 a electrically connectsthe first energy input/output unit 300 and the first output converter318 to each other, while the third switcher 314 c and the fifth switcher314 e electrically connect the first output converter 318 and thebattery 308 to each other. Similarly, for inputting electric power viathe second energy input/output unit 302, the second switcher 314 belectrically connects the second energy input/output unit 302 and thesecond input converter 320 to each other, while the fourth switcher 314d and the fifth switcher 314 e electrically connect the second inputconverter 320 and the battery 308 to each other. Conversely, foroutputting electric power via the second energy input/output unit 302,the second switcher 314 b electrically connects the second energyinput/output unit 302 and the second output converter 322 to each other,while the fourth switcher 314 d and the fifth switcher 314 eelectrically connect the second output converter 322 and the battery 308to each other. The first through fifth switchers 314 a through 314 e arecontrolled by an electric power supply controller 374, to be describedlater, in order to make such connections.

The first energy input/output unit 300, the second energy input/outputunit 302, the first energy converter 310, and the second energyconverter 312 have different structures depending on the type of energyto be supplied (supplied energy).

For example, if electric energy is supplied through wired connectionssuch as cables, connection terminals, etc., then the first energyinput/output unit 300 comprises a connector, which is connected tocables and connection terminals. The first input converter 316 comprisesa voltage converter or the like for converting a voltage applied fromthe first energy input/output unit 300 through the first switcher 314 ainto a voltage that is optimum for charging the battery 308. The firstoutput converter 318 comprises a voltage converter or the like forconverting a voltage output from the battery 308 through the fifthswitcher 314 e and the third switcher 314 c into a voltage that isoptimum for power transmission. The second energy input/output unit 302and the second energy converter 312 also are of a similar construction.

If electric energy is supplied by way of electromagnetic inductionthrough a coil (primary coil or secondary coil) embedded in acontactless power transmission sheet, for example as disclosed inDocument 3, then the first energy input/output unit 300 comprises asecondary coil or a primary coil, whereas the first input converter 316comprises a voltage converter or the like for converting a voltagegenerated by the first energy input/output unit 300, which functions asa secondary coil, into a voltage that is optimum for charging thebattery 308. Further, the first output converter 318 comprises avoltage-to-current converter for converting a voltage output from thebattery 308 through the fifth switcher 314 e and the third switcher 314c into a current that flows to the first energy input/output unit 300,which functions as a primary coil. The second energy input/output unit302 and the second energy converter 312 also are of a similarconstruction.

If electric energy is supplied by way of wireless power transmissiontechnology based on magnetic resonance as disclosed in Document 4, thenthe first energy input/output unit 300 comprises a second LC resonatoror a first LC resonator, which is combined with a first LC resonator ora second LC resonator of an electric power transmitter, whereas thefirst input converter 316 comprises a coil, i.e., a secondary coilcombined with a primary coil as the coil of the second LC resonator, forconverting electromagnetic energy generated by the first energyinput/output unit 300, which functions as the second LC resonator.Further, the first output converter 318 comprises a coil, i.e., aprimary coil combined with a secondary coil as the coil of the first LCresonator, for outputting a voltage output from the battery 308 throughthe fifth switcher 314 e and the third switcher 314 c as electromagneticenergy from the first energy input/output unit 300, which functions asthe first LC resonator. The second energy input/output unit 302 and thesecond energy converter 312 also are of a similar construction.

The supplied energy may be optical energy or thermal energy. If thesupplied energy is optical energy, then an energy receiver is provided,which comprises a photodetector for detecting optical energy, and anenergy converter is provided, which comprises a photoelectric transducer(photoelectric converter) for converting the detected optical energyinto electric power. If the supplied energy is thermal energy, then anenergy receiver is provided, which comprises a thermal sensor fordetecting thermal energy, and an energy converter is provided, whichcomprises a thermoelectric transducer, i.e., a thermoelectric transducerbased on the Seebeck Effect, for converting the detected thermal energyinto electric power.

The battery 308 may comprise a secondary battery, such as a nickelhydrogen battery, a nickel cadmium battery, a lithium battery, or thelike, or a capacitor, such as a catalytic capacitor, an electricdouble-layer capacitor, a lithium ion capacitor, or the like. Thebattery 308 may be detachably mounted on the cassette 12. The battery308 may comprise a small-size built-in capacitor, which is capable ofstoring an amount of electric power required to capture at least oneradiographic image.

Since the transceiver 94 is capable of sending signals to and receivingsignals from an external circuit, the transceiver 94 can send signals toand receive signals from a transceiver 98 (see FIG. 11) of the mobileterminal 42, which is removed from the recess 54, and also can sendsignals to and receive signals from a transceiver 100 of the radiationsource device 18, which is separated from the cassette 12. Even when thecassette 12 and the radiation source device 18 are integrally coupled toeach other and/or if the mobile terminal 42 is placed in the recess 54,the transceiver 94 can send signals to and receive signals from thetransceivers 98, 100.

As shown in FIG. 5, the radiation source device 18 houses therein theradiation source 44, a battery unit 304, a battery controller 306 forcontrolling the battery unit 304, a transceiver 100, a radiation sourcecontroller 102 for controlling the radiation source 44, and a laserpointer 104. The first energy input/output unit 300 and the secondenergy input/output unit 302, which are identical to those provided onthe cassette 12, are mounted on a side wall of the casing of theradiation source device 18.

The radiation source 44 comprises a field-electron-emission-typeradiation source, which is similar to the field-electron-emission-typeradiation source disclosed in Japanese Laid-Open Patent Publication No.2007-103016.

The radiation source 44 includes a disk-shaped rotary anode 110 mountedon a rotational shaft 108, which can be rotated about its axis by arotating mechanism 106, an annular target layer 112 disposed on thesurface of the rotary anode 110 and made up principally from a metallicelement such as Mo or the like, a cathode 114 disposed in confrontingrelation to the rotary anode 110, and a field-electron-emission-typeelectron source 116 disposed on the cathode 114 in confronting relationto the target layer 112.

When the operator 38 operates the exposure switch 48, the radiationsource controller 102 controls the radiation source 44 to outputradiation 46. More specifically, when the radiation source 44 iscontrolled by the radiation source controller 102, the rotatingmechanism 106 rotates the rotational shaft 108 so as to rotate therotary anode 110. The battery unit 304 supplies electric power to apower supply 118, which applies a negative voltage to thefield-electron-emission-type electron source 116. The battery unit 304also supplies electric power to a power supply 120, which applies avoltage between the rotary anode 110 and the cathode 114. Morespecifically, a positive voltage is applied to the rotary anode 110,whereas a negative voltage is applied to the cathode 114. Thefield-electron-emission-type electron source 116 emits electrons, whichare accelerated and bombard the target layer 112 due to the voltageapplied between the rotary anode 110 and the cathode 114. The electronsare focused onto a focus point 122 on the surface of the target layer112, and the bombarded surface of the target layer 112 emits radiation46 from the focus point 122 at an intensity level depending on theapplied electrons. As the radiation source 44, a portable size and highenergy X-ray source that is disclosed in Document 2 and uses a crystalof tourmaline, LiNbO₃, LiTaO₃, ZnO, and the like, may be employed. Inthis case, for example, about 100 kV voltage can be generated by usingLiNbO₃, whose axial length is 1 cm.

For irradiating the subject 50 with radiation 46 in order to captureradiographic images of the subject 50, it is necessary first to performa preparatory procedure, thus readying the first radiographic imagecapturing apparatus 10A for capturing radiographic images. Thepreparatory procedure includes a process for presetting asource-to-image distance (SID), which represents the distance (imagingdistance) between the focus point 122 of the radiation source 44 and aposition 124 (see FIG. 6) on the radiation detector 86 located directlybeneath the focus point 122, and a process for bringing the center of arange within which the irradiated surface 20 is irradiated withradiation 46 into alignment with a central position 126, i.e., a pointof intersection, of the aforementioned crisscross guide lines 22.

The preparatory procedure is carried out as follows. As shown in FIGS. 6and 7, while the radiation source device 18 is separated from thecassette 12, the operator 38 pulls the ribbon 76 from the tape measure72 until the length of the ribbon 76, which is reeled out from the tapemeasure 72, is equal to a reeled-out length 11 that depends on the SID.The laser pointer 104 is controlled by the radiation source controller102 to apply and focus a laser beam 128 on the irradiated surface 20, inorder to display a crisscross mark 130 on the irradiated surface 20,which represents the center of a range within which the irradiatedsurface 20 is irradiated with radiation 46.

The SID, the reeled-out length 11 that depends on the SID, and adistance 12 between the position 124 or the central position 126 and theside 14 a, which has the hole 80 through which the ribbon 76 is pulledout, are related to each other according to the equationSID≈(11²−12²)^(1/2). The distance 12 is constant.

After the ribbon 76 has been pulled out from the tape measure 72 by thereeled-out length 11, the operator 38 positionally adjusts the radiationsource device 18 so as to bring the mark 130 displayed on the irradiatedsurface 20 into alignment with the central position 126. Thereafter, theoperator 38 turns on the exposure switch 48 to cause the radiationsource 44 to apply radiation 46 to the subject 50 on the irradiatedsurface 20, thereby capturing radiographic images of the subject 50, asshown in FIG. 8. In FIG. 8, an example is shown in which a radiographicimage of a hand of the subject 50 is captured.

As shown in FIG. 9, the radiation detector 86 comprises a number ofpixels 132 arrayed on a substrate, not shown, a number of gate lines 134for supplying control signals to the pixels 132, and a number of signallines 136 for reading electric signals output from the pixels 132.

A circuit arrangement of the radiation detector 86, which is of anindirect conversion type, for example, that is housed in the cassette12, will be described in detail below with reference to FIG. 10.

As shown in FIG. 10, the radiation detector 86 comprises an array ofthin-film transistors (TFTs) 140 arranged in rows and columns, and aphotoelectric conversion layer 138 including the pixels 132, and made ofa material such as amorphous silicon (a-Si) or the like for convertingvisible light into analog electric signals. The photoelectric conversionlayer 138 is disposed on the array of TFTs 140. When radiation 46 isapplied to the radiation detector 86, the pixels 132 generate electriccharges by converting visible light into analog electric signals. Then,when the TFTs 140 are turned on one row at a time, electric charges areread from the pixels 132 as image signals.

The TFTs 140 are connected respectively to the pixels 132. The gatelines 134, which extend parallel to the rows, and the signal lines 136,which extend parallel to the columns, are connected to the TFTs 140. Thegate lines 134 are connected to a line scanning driver 142, and thesignal lines 136 are connected to a multiplexer 144. The gate lines 134are supplied with control signals Von, Voff from the line scanningdriver 142 for turning on and off the TFTs 140 along the rows. The linescanning driver 142 comprises a plurality of switches SW1 for switchingbetween the gate lines 134, and an address decoder 146 for outputting aselection signal for selecting one of the switches SW1 at a time. Thecassette controller 92 supplies an address signal to the address decoder146.

The signal lines 136 are supplied with electric charges stored by thepixels 132 through the TFTs 140 arranged in the columns. The electriccharges supplied to the signal lines 136 are amplified by amplifiers148, which are connected respectively to the signal lines 136. Theamplifiers 148 are connected through respective sample and hold circuits150 to the multiplexer 144. The multiplexer 144 comprises a plurality ofswitches SW2 for successively switching between the signal lines 136,and an address decoder 152 for outputting selection signals forselecting one of the switches SW2 at a time. The address decoder 152 issupplied with an address signal from the cassette controller 92. Themultiplexer 144 has an output terminal connected to an A/D converter154. Radiographic image signals, which are generated by the multiplexer144 based on electric charges from the sample and hold circuits 150, areconverted by the A/D converter 154 into digital image signalsrepresenting radiographic image information, which is supplied to thecassette controller 92.

The TFTs 140, which function as switching devices, may be combined withanother image capturing device, such as a CMOS (ComplementaryMetal-Oxide Semiconductor) image sensor or the like. Alternatively, theTFTs 140 may be replaced with a CCD (Charge-Coupled Device) image sensorfor shifting and transferring electric charges with shift pulses thatcorrespond to gate signals in the TFTs.

FIG. 11 shows in block form the first radiographic image capturingapparatus 10A. Components of the first radiographic image capturingapparatus 10A, which have not been described above with reference toFIGS. 1 through 10, will mainly be described below with reference toFIG. 11.

The cassette controller 92 comprises an address signal generator 162, animage memory 164, and an SID determining unit (imaging distancedetermining unit) 168.

The address signal generator 162 supplies address signals to the addressdecoder 146 of the line scanning driver 142, as well as to the addressdecoder 152 of the multiplexer 144. The image memory 164 stores theradiographic image information detected by the radiation detector 86.

The SID determining unit 168 calculates the imaging distance between thefocus point 122 and the position 124, at a time when the radiationsource device 18 is tentatively placed over the irradiated surface 20according to the present reeled-out length 11 of the ribbon 76, based onthe reeled-out length 11 of the ribbon 76, which is input from therotary encoder 78, and the stored distance 12.

If the calculated imaging distance agrees with the SID, the SIDdetermining unit 168 controls the display unit 36 through thetransceivers 94, 98, so as to display information representing thepresent reeled-out length of the ribbon 76 as the reeled-out length 11that depends on the SID, and also to display information representingthat the imaging distance agrees with the SID. The cassette 12 mayinclude a mechanism for preventing (locking) the ribbon 76 from beingreeled out further, when the reeled-out length 11 and the imagingdistance have been determined to agree with the SID. If the calculatedimaging distance does not agree with the SID, then the SID determiningunit 168 controls the display unit 36 through the transceivers 94, 98 inorder to display information representing the difference between thepresent reeled-out length and the reeled-out length 11, and also todisplay information representing that the imaging distance does notagree with the SID.

The SID determining unit 168, the rotary encoder 78, and the tapemeasure 72 jointly make up an imaging distance setting means 169.

The cassette controller 92 transmits cassette ID information of thecassette 12 and radiographic image information, which are stored in theimage memory 164, via the transceiver 94 to the mobile terminal 42 byway of wireless communications.

A preparatory procedure using the cassette 12 and the radiation sourcedevice 18, as well as operations of the first radiographic imagecapturing apparatus 10A to capture radiographic images, shall bedescribed below.

First, the operator 38 performs an operation to ready the firstradiographic image capturing apparatus 10A for capturing radiographicimages at a site where the first radiographic image capturing apparatus10A has been carried. The operator 38 operates the operating unit 40 ofthe mobile terminal 42 in order to register image capturing conditionsincluding subject information (e.g., SID) of the subject 50 to beimaged.

At this time, the operator 38 operates the operating unit 40 while themobile terminal 42 either is detached from or placed within the recess54. If the body region to be imaged and an image capturing method areknown, then the operator 38 also operates the operating unit 40 in orderto register the body region and the image capturing method as imagecapturing conditions. If details of the subject 50 are already knownbefore the operator 38 carries the first radiographic image capturingapparatus 10A to the imaging site, then the operator 38 may register thesubject information including such details using the mobile terminal 42,which is located at the medical organization, e.g., the hospital, wherethe subject 50 is being treated.

The registered image capturing conditions, including subject informationof the subject 50, are sent from the transceiver 98 of the mobileterminal 42 to the transceiver 94 of the cassette 12 by way of wirelesscommunications, whereupon the image capturing conditions are registeredin the cassette controller 92.

When the operator 38 presses the unlocking button 34, the hook 64 isdisplaced toward the side wall 52 d against the resiliency of the spring60 until the hook 64 is brought out of engagement with the edge of thethrough hole 66.

When the operator 38 detaches the radiation source device 18 from thecassette 12 while the hook 64 does not engage with the edge of thethrough hole 66, i.e., while the operator 38 presses the unlockingbutton 34, then the connection terminal 68 a becomes disengaged from theconnection terminal 70 a, and the connection terminal 68 b becomesdisengaged from the connection terminal 70 b, thereby releasing theradiation source device 18 and the cassette 12 from each other.

The operator 38 sets the imaging distance and then brings the mark 130,which is displayed on the irradiated surface 20, into alignment with thecentral position 126 of the guide lines 22. Thereafter, the operator 38places and positions the subject 50 between the irradiated surface 20and the radiation source device 18.

The operator 38 moves the radiation source device 18, whereby the ribbon76 is reeled out from the tape measure 72 until the actual reeled-outlength of the ribbon 76 reaches the reeled-out length 11 that depends onthe SID.

The ribbon 76 is reeled out from the tape measure 72 until the actualreeled-out length of the ribbon 76 reaches the reeled-out length 11, inaccordance with either of the two processes described below.

According to the first process, the SID determining unit 168automatically determines whether or not the actual reeled-out length ofthe ribbon 76 has reached the reeled-out length 11. Therefore, theoperator 38 is able to reel out the ribbon 76 from the tape measure 72until the actual reeled-out length of the ribbon 76 reaches thereeled-out length 11 that depends on the SID.

In the first process, the rotary encoder 78 detects the actualreeled-out length of the ribbon 76, and based on the detected reeled-outlength, the SID determining unit 168 calculates the imaging distancebetween the focus point 122 and the position 124 when the radiationsource device 18 is tentatively placed over the irradiated surface 20 inaccordance with the present reeled-out length of the ribbon 76.

If the imaging distance agrees with the SID, then the SID determiningunit 168 controls the display unit 36 via the transceivers 94, 98 todisplay information representing the reeled-out length of the ribbon 76,and also to display information representing that the imaging distanceagrees with the SID. If the imaging distance does not agree with theSID, then the SID determining unit 168 controls the display unit 36 viathe transceivers 94, 98 to display information representing thedifference between the present reeled-out length and the reeled-outlength 11, and also to display information representing that the imagingdistance does not agree with the SID.

The first process allows the operator 38 to set the imaging distanceeasily, because the operator 38 may reel out the ribbon 76 from the tapemeasure 72 according to the information displayed on the display unit36.

According to the second process, the reeled-out length 11 already isknown, and the operator 38 reels out the ribbon 76 from the tape measure72, while observing the graduations 74, until the present reeled-outlength reaches the reeled-out length 11.

After the ribbon 76 has been reeled out from the tape measure 72 untilthe present reeled-out length reaches the reeled-out length 11 thatdepends on the SID, the operator 38 moves the radiation source device 18so as to confront (i.e., be placed in a facing relationship with) theirradiated surface 20.

At this time, the radiation source controller 102 controls the laserpointer 104 to apply a laser beam 128 to the irradiated surface 20. Thecrisscross mark 130, which represents the center of a range within whichthe irradiated surface 20 is irradiated with radiation 46, is displayedon the irradiated surface 20. The operator 38 positionally adjusts theradiation source device 18 until the mark 130 and the central position126 are aligned with each other.

After having adjusted the position of the radiation source device 18until the mark 130 and the central position 126 are aligned with eachother, the operator 38 places or positions the subject 50 on theirradiated surface 20, so that the center of a body region of thesubject 50 to be imaged is aligned with the central position 126, i.e.,is aligned with the position of the mark 130.

After the above positional adjustment has been made, the radiationsource device 18 is secured at the adjusted position by a holder, notshown, for example.

At a site such as a disaster site, due to limited space availability,the first radiographic image capturing apparatus 10A may not be able tocapture radiographic images with the desired SID. Therefore, thecassette controller 92 may recalculate image capturing conditions basedon a new SID, which is different from the desired SID, and store therecalculated image capturing conditions together with the new SID inassociation with image data, or transmit the new SID and/or therecalculated image capturing conditions via a network to a data centersuch as a medical organization for confirmation.

After the subject 50 has been positioned, the operator 38 turns on theexposure switch 48 to begin capturing radiographic images of the subject50.

When the exposure switch 48 is turned on, the radiation sourcecontroller 102 sends a request for image capturing conditions to thecassette controller 92 by way of wireless communications. Based on sucha request, the cassette controller 92 sends the image capturingconditions (control signals) with respect to the body region of thesubject 50 to be imaged to the radiation source device 18. When theradiation source controller 102 receives the image capturing conditions,the radiation source controller 102 controls the laser pointer 104 inorder to stop emitting the laser beam 128, and controls the radiationsource 44 to apply radiation 46 at a predetermined dose to the subject50.

In the radiation source 44, the rotating mechanism 106 is controlled bythe radiation source controller 102 in order to rotate the rotationalshaft 108 and the rotary anode 110. The power supply 118 applies anegative voltage to the field-electron-emission-type electron source116, and the power supply 120 applies a voltage between the rotary anode110 and the cathode 114, based on electric power supplied from thebattery unit 304. The field-electron-emission-type electron source 116emits electrons, which are accelerated by the voltage applied betweenthe rotary anode 110 and the cathode 114, and the electrons bombard thetarget layer 112. The surface of the target layer 112, which isbombarded with electrons, emits radiation 46 from the focus point 122,the intensity of which depends on the applied electrons.

While the subject 50 is irradiated with radiation 46 for a givenirradiation time based on the image capturing conditions, the radiation46 passes through the subject 50 and reaches the radiation detector 86of the cassette 12.

Since the radiation detector 86 is of an indirect conversion type, thescintillator of the radiation detector 86 emits visible light having anintensity that depends on the intensity of the radiation 46, and thepixels 132 of the photoelectric conversion layer 138 convert the visiblelight into electric charges and store the electric charges. The electriccharges stored by the pixels 132, which are representative of aradiographic image of the subject 50, are read from the pixels 132according to address signals, which are supplied from the address signalgenerator 162 of the cassette controller 92 to the line scanning driver142 and the multiplexer 144.

More specifically, in response to an address signal supplied from theaddress signal generator 162, the address decoder 146 of the linescanning driver 142 outputs a selection signal in order to select one ofthe switches SW1, which supplies the control signal Von to the gates ofthe TFTs 140 that are connected to the gate line 134 corresponding tothe selected switch SW1. In response to address signals supplied fromthe address signal generator 162, the address decoder 152 of themultiplexer 144 outputs selection signals to successively turn on theswitches SW2 so as to switch between the signal lines 136, for therebyreading through the signal lines 136 the electric charges stored in thepixels 132 that are connected to the selected gate line 134.

The electric charges, which are read from the pixels 132 connected tothe selected gate line 134, are amplified respectively by the amplifiers148, sampled by the sample and hold circuits 150, and supplied to themultiplexer 144. Based on the supplied electric charges, the multiplexer144 generates and supplies radiographic image signals to the A/Dconverter 154, which converts the radiographic image signals intodigital signals. Digital signals representative of the radiographicimage information are stored in the image memory 164 of the cassettecontroller 92.

Similarly, the address decoder 146 of the line scanning driver 142successively turns on the switches SW1 so as to switch between the gatelines 134 according to the address signals supplied from the addresssignal generator 162. Electric charges stored in the pixels 132connected to the successively selected gate lines 134 are read throughthe signal lines 136, processed by the multiplexer 144, and convertedinto digital signals by the A/D converter 154. The digital signals arestored in the image memory 164 of the cassette controller 92.

Radiographic image information represented by the digital signals storedin the image memory 164 is transmitted through the transceiver 94 to themobile terminal 42 by way of wireless communications. Radiographic imageinformation transmitted to the mobile terminal 42 is received by thetransceiver 98, and is transmitted from the transceiver 98 to thedisplay unit 36, which displays a radiographic image based on theradiation image information, as shown in FIG. 12. The operator 38 candetermine whether or not the body region of the subject 50 to be imagedhas been appropriately imaged by confirming the radiographic imagedisplayed on the display unit 36.

For example, if the radiographic image displayed on the display unit 36does not include the body region of the subject 50 to be imaged, thenthe operator 38 judges that the subject 50 has not been appropriatelyimaged, and captures another radiographic image of the subject 50. Atthis time, using the mobile terminal 42, the operator 38 updates thenumber of captured images in the image capturing conditions, byincrementing the number with the number of recaptured images.

The radiographic image displayed on the display unit 36 may be of aquality that is sufficient enough to determine whether or not thesubject 50 has been appropriately imaged. The displayed radiographicimage may either be a radiographic image represented by the radiographicimage information stored in the image memory 164, an image of low data,or a relatively low resolution processed image.

As shown in FIG. 14, the battery controller 306 comprises a memory 330,an activator/deactivator 332, an electric power supply permissioninstructing unit 350, an electric power supply activator 336, anelectric power controller 334, an electric power supply limiter (imagecapturing process indicating unit) 338, and a pause processor 340.

The activator/deactivator 332 comprises a selected one of a firstactivator/deactivator 332A, a second activator/deactivator 332B, and athird activator/deactivator 332C, which will be described below.

The first activator/deactivator 332A detects the present position ofdevices that incorporate the battery controller 306, i.e., the radiationsource device 18, the cassette 12, etc., determines whether or not thedetected present position is outside of a medical organization, andfurther determines whether or not supply of electric power between thedevices is to be activated. If the present position is outside of themedical organization, then the first activator/deactivator 332A outputsan activation signal. If the present position changes and enters themedical organization after supply of electric power between the deviceshas been activated, then the first activator/deactivator 332A outputs afull deactivation signal. If the present position changes again andexits the medical organization after the first activator/deactivator332A has output the full deactivation signal, then the firstactivator/deactivator 332A outputs an activation signal.

The second activator/deactivator 332B detects the present position ofdevices that incorporate the battery controller 306, i.e., the radiationsource device 18, the cassette 12, etc., determines whether or not thedetected present position is a preset position or not, and determineswhether supply of electric power between the devices is to be activated.If the present position is the preset position, then the secondactivator/deactivator 332B outputs an activation signal. If the presentposition changes and leaves the preset position after supply of electricpower between the devices has been activated, then the secondactivator/deactivator 332B outputs a full deactivation signal. If thepresent position changes again and reaches the preset position after thesecond activator/deactivator 332B has output the full deactivationsignal, then the second activator/deactivator 332B outputs an activationsignal.

The third activator/deactivator 332C determines whether the distancebetween devices that incorporate the battery controller 306, i.e., theradiation source device 18, the cassette 12, etc., and which belong tothe first radiographic image capturing apparatus 10A, satisfies acertain condition or not, and determines whether or not supply ofelectric power between the devices is to be activated. If the distancesatisfies the certain condition, then the third activator/deactivator332C outputs an activation signal. If the distance changes and does notsatisfy the certain condition after supply of electric power between thedevices has been activated, then the third activator/deactivator 332Coutputs a full deactivation signal. If the distance changes again andsatisfies the certain condition after the third activator/deactivator332C has output the full deactivation signal, then the thirdactivator/deactivator 332C outputs an activation signal.

The electric power supply permission instructing unit 350 outputs amessage for prompting entry of image capturing conditions to the mobileterminal 42, for example, based on the activation signal input from theactivator/deactivator 332.

The electric power supply activator 336 activates the electric powercontroller 334 based on the activation signal input from theactivator/deactivator 332, and deactivates the electric power controller334 based on the full deactivation signal input from theactivator/deactivator 332.

The electric power controller 334 is activated by the electric powersupply activator 336 so as to allow electric power to be suppliedbetween the batteries 308 (see FIG. 13) in the devices, which areconnected in a wired fashion, or between the devices that have enteredinto an area where they can be fed wirelessly, i.e., devices that areconnected in a wireless fashion.

If the activator/deactivator 332 has decided to activate supply ofelectric power between the devices, then since it is possible to supplyelectric power using the cassette 12 and the radiation source device 18of the first radiographic image capturing apparatus 10A, it also ispossible to supply electric power between either one of these devicesand other devices, i.e., devices of another first radiographic imagecapturing apparatus 10A. For example, it is possible to supply electricpower between the radiation source device 18, which is used to captureradiographic images, and the cassette 12 combined therewith, between aradiation source device 18 that is not used to capture radiographicimages and the cassette 12 referred to above, and between a cassette 12that is not used to capture radiographic images and the cassette 12referred to above.

The electric power supply limiter 338 limits operation of the electricpower controller 334 so as to supply electric power only during periodsin which radiographic images are being captured.

The pause processor 340 temporarily shuts down the electric powercontroller 334 at a time when capturing of radiographic images iscompleted, or when supply of electric power is terminated.

The activator/deactivator 332, the electric power supply permissioninstructing unit 350, the electric power supply activator 336, theelectric power controller 334, etc., which have been referred to above,will be described in detail later.

The memory 330 stores ID information for identifying the devicesincorporating the battery controller 306, i.e., the cassette 12, theradiation source device 18, etc., and also stores various conditions.The memory 330 also temporarily stores various table information, whichmay be entered via a network, the mobile terminal 42, etc.

Details of the first activator/deactivator 332A, the secondactivator/deactivator 332B, and the third activator/deactivator 332Cwill be described below with reference to FIGS. 15A through 17C.

The first activator/deactivator 332A is available in differentconfigurations according to two modes, i.e., a first mode and a secondmode. According to the first mode, as shown in FIG. 15A, the firstactivator/deactivator 332A detects a present position of the firstradiographic image capturing apparatus 10A utilizing GPS (GlobalPositioning System). The first activator/deactivator 332A according tothe first mode comprises a GPS antenna 342, a GPS receiver 344, a firstpresent position acquirer 346A, a first activation determiner 348A, anda first location information table 331A. According to the second mode,as shown in FIG. 15B, it is assumed that the operator 38 uses a car orthe like to carry a portable radiographic image capturing apparatus, orcarries the first radiographic image capturing apparatus 10A while alsocarrying a portable navigation system 352 (such as a mobile phone or thelike). The first activator/deactivator 332A according to the second modecomprises a first present position acquirer 346A, a first activationdeterminer 348A, and a first location information table 331A.

The first activator/deactivator 332A according to the first mode, whichis shown in FIG. 15A, operates in the following manner. The GPS receiver344 acquires a GPS signal (comprising positional information of anartificial satellite, and a time at which radio waves are transmittedfrom the artificial satellite) received by the GPS antenna 342. Thefirst present position acquirer 346A calculates the present position(first present position) of the first radiographic image capturingapparatus 10A based on the acquired GPS signal, and informationconcerning the time at which radio waves from the artificial satelliteare received.

The first activator/deactivator 332A according to the second mode shownin FIG. 15B operates in the following manner. The first present positionacquirer 346A acquires positional information from the navigation system352 as a present position (first present position) of the firstradiographic image capturing apparatus 10A.

In each of the first activator/deactivators 332A according to the firstand second modes, the first activation determiner 348A compares thefirst present position, which is acquired by the first present positionacquirer 346A, with the positional information of a medical organizationthat is registered in the first location information table 331A, anddetermines whether or not the present position is outside of the medicalorganization. The position of the medical organization in theneighborhood of the first present position may be obtained from a mappublishing company database, and is registered in the first locationinformation table 331A, which may be stored in the memory 330.Alternatively, if the first radiographic image capturing apparatus 10Ais carried into a predetermined area, then the position of the medicalorganization in the neighborhood of the predetermined area may beregistered in a USB memory, and is read from the USB memory andregistered in the first location information table 331A, which may bestored in the memory 330. Positional information of the medicalorganization refers to information, which represents an area having aradius ranging from 10 to 200 meters from the center of the medicalorganization, for example. The first activation determiner 348A comparesthe area with the first present position in order to determine whetheror not the first present position lies within the area. Then, the firstactivation determiner 348A judges that the present position is outsideof the medical organization if the first present position is not withinthe area, and outputs an activation signal. Alternatively, if the firstactivation determiner 348A judges that the first present position lieswithin the area, then the first activation determiner 348A outputs afull deactivation signal.

The second activator/deactivator 332B is available in configurationsaccording to two modes, i.e., a first mode and a second mode. Accordingto the first mode, as shown in FIG. 16A, the secondactivator/deactivator 332B detects the present position (second presentposition) of the first radiographic image capturing apparatus 10Autilizing GPS. The second activator/deactivator 332B according to thefirst mode comprises a GPS antenna 342, a GPS receiver 344, a secondpresent position acquirer 346B, a second activation determiner 348B, anda second location information table 331B. According to the second mode,as shown in FIG. 16B, it is assumed that the operator 38 uses a car orthe like to carry a portable radiographic image capturing apparatus, orcarries the first radiographic image capturing apparatus 10A while alsocarrying a portable navigation system 352 (such as a mobile phone or thelike). The second activator/deactivator 332B according to the secondmode comprises a second present position acquirer 346B for acquiringpositional information from the navigation system 352, a secondactivation determiner 348B, and a second location information table331B.

In the second activator/deactivator 332B according to each of the firstand second modes, the second activation determiner 348B compares thesecond present position, which is acquired by the second presentposition acquirer 346B, with area information that is registered in thesecond location information table 331B, i.e., area informationrepresentative of a preset location, and determines whether or not thesecond present position is in the preset location.

The area information is registered in the second location informationtable 331B by a location setting unit 353 (see FIGS. 16A and 16B), whichis incorporated in the mobile terminal 42, or in a computer at the datacenter (medical organization).

The area information, which is registered in the second locationinformation table 331B, includes area information by way of absolutepositioning as well as area information by way of relative positioning.Area information by way of absolute positioning refers to informationrepresentative of an area having a radius ranging from 10 to 200 metersfrom a position represented by positional information of a fixedlocation, such as a building, a land location, or the like. Areainformation by way of relative positioning refers to informationrepresentative of an area having a radius ranging from 10 to 200 metersfrom a position represented by positional information of a moving object(location), in the form of a transport vehicle such as an ambulance, amobile medical checkup motor vehicle, a railway car, a ship, anaircraft, or the like. Flag information (“0”: absolute positioning, “1”:relative positioning) applied to the area information may be used todetermine whether the registered area information is area information byway of absolute positioning or area information by way of relativepositioning.

A process for setting area information by way of absolute positioningwill be described below. The location setting unit 353, which isincorporated in a computer at the data center, sets area information byway of absolute positioning by acquiring positional information of adisaster site or an accident site (information of a present positionbased on GPS) indicated by an external source, and registeringinformation representative of an area having a radius ranging from 10 to200 meters from the position represented by the acquired positionalinformation, as area information representative of the disaster site orthe accident site, in the second location information table 331B in adatabase of the data center. Usually, a public organization, such as anadministrative institution, a fire department, a police department, orthe like, serves as the external source that indicates the disaster siteor the accident site. However, an operator 38 who works for a medicalorganization may witness a disaster site or an accident site, and maysend the present position to the data center using a present positionsending function of a mobile phone possessed by the operator 38.

A medical organization site, a medical checkup site, or a home-careservice site is set by acquiring positional information, whichrepresents the address of a medical organization that does not have aradiation facility, such as a clinic or the like, a place where amedical checkup is to be carried out, or a home receiving home-careservices, from the database of a map publishing company, and registeringinformation representative of an area having a radius ranging from 10 to200 meters from the position represented by the acquired positionalinformation, and flag information representative of the absoluteposition thereof, as area information representative of the medicalorganization site, the medical checkup site, or the home-care servicesite, in the second location information table 331B.

A computer at the data center also sets area information by way ofabsolute positioning when the operator 38 who carries the firstradiographic image capturing apparatus 10A sends information of thepresent position of the operator 38 to the data center using the mobileterminal 42, at a time when the operator 38 arrives at the medicalorganization, the accident site, the disaster site, the medical checkupsite, or the home-care service site. The computer at the data centeracquires information of the present position sent from the mobileterminal 42 by the operator 38, and registers information representativeof an area having a radius ranging from 10 to 200 meters from theposition represented by the acquired positional information, and flaginformation representative of the absolute position thereof, as areainformation representative of a preset location, in the second locationinformation table 331B.

After having registered the second location information table 331B inthe database, the location setting unit 353, which is incorporated inthe computer at the data center, sends the second location informationtable 331B to the mobile terminal 42 of the first radiographic imagecapturing apparatus 10A. Upon receiving the second location informationtable 331B, the mobile terminal 42 sends the second location informationtable 331B to the battery controller 306. The battery controller 306then stores the received second location information table 331B in thememory 330.

The location setting unit 353, which is incorporated in the mobileterminal 42, sets area information by way of absolute positioning whenthe operator 38 enters an operation input into the mobile terminal 42 inorder to activate the location setting unit 353, and the locationsetting unit 353 designates the present position of the operator 38 as apreset location. The location setting unit 353 registers informationrepresentative of an area having a radius ranging from 10 to 200 metersfrom the designated present position, and flag informationrepresentative of the absolute position thereof, as area informationrepresentative of the preset location, in the second locationinformation table 331B. Thereafter, the location setting unit 353 sendsthe second location information table 331B to the data center forsharing the second location information table 331B. The data centersends the received second location information table 331B to othermobile terminals 42, so that the second location information table 331Bcan be shared among the mobile terminals 42.

A process of setting area information by way of relative positioningwill be described below. When the operator 38 who carries the firstradiographic image capturing apparatus 10A is on board a transportvehicle, such as an ambulance, a mobile medical checkup motor vehicle, arailway car, a ship, an aircraft, or the like, the operator 38 sendsinformation concerning the present position of the operator 38 togetherwith a code representative of the relative position to the data center.The location setting unit 353 at the data center acquires theinformation of the present position of the operator 38, which was sentby the operator 38 from the mobile terminal 42, acquires the presentposition of the transport vehicle from a transport vehicle managementcenter corresponding to the present position based on the coderepresentative of the relative position, and registers informationrepresentative of an area having a radius ranging from 10 to 200 metersfrom the present position, and flag information representative of therelative position thereof, as area information representative of thepreset location, in the second location information table 331B.Thereafter, the location setting unit 353 acquires the present positionof the transport vehicle periodically, for example, at time intervalsfrom 1 to 10 minutes, from the transport vehicle management center, andrepeatedly updates and registers information representative of an areahaving a radius ranging from 10 to 200 meters from the present position,as area information representative of the preset location, in the secondlocation information table 331B. Each time that the location settingunit 353 periodically updates and registers the area informationrepresentative of the preset location in the second location informationtable 331B, the location setting unit 353 sends the second locationinformation table 331B to the mobile terminal 42 of the firstradiographic image capturing apparatus 10A. After the mobile terminal 42has received the second location information table 331B, the mobileterminal 42 sends the second location information table 331B to thebattery controller 306. The battery controller 306 then stores thereceived second location information table 331B in the memory 330. Thelocation setting unit 353 may send only area information representativeof the relative position to the mobile terminal 42 of the firstradiographic image capturing apparatus 10A.

The location setting unit 353, which is incorporated in the mobileterminal 42, sets area information by way of relative positioning whenthe operator 38, who is on board the transport vehicle, enters anoperation input into the mobile terminal 42 in order to activate thelocation setting unit 353, designates the present position of theoperator as a preset location, and further designates the position as arelative position. Based on the code representative of the relativeposition, the location setting unit 353 acquires the present position ofthe transport vehicle from the transport vehicle management centercorresponding to the information representative of the present position,and registers information representative of an area having a radiusranging from 10 to 200 meters from the position and flag informationrepresentative of the relative position thereof, as area informationrepresentative of the relative position, in the second locationinformation table 331B, which may be stored in the memory 330.Thereafter, the location setting unit 353 acquires the present positionof the transport vehicle periodically, for example, at time intervalsfrom 1 to 10 minutes, from the transport vehicle management center, andrepeatedly updates and registers information representative of an areahaving a radius ranging from 10 to 200 meters from the present position,as area information representative of the preset location, in the secondlocation information table 331B. Each time that the location settingunit 353 periodically updates and registers the area informationrepresentative of the preset location in the second location informationtable 331B, the location setting unit 353 sends the second locationinformation table 331B to the data center for enabling sharing of thesecond location information table 331B. The data center sends thereceived second location information table 331B to other mobileterminals 42 for enabling the second location information table 331B tobe shared among the mobile terminals 42. A transport vehicle, such as anambulance or a mobile medical checkup motor vehicle, may be parked for arelatively long time of 30 minutes or longer for diagnosing a patient.In such a case, area information by way of absolute positioning may beregistered in the second location information table 331B.

The second activation determiner 348B compares the second presentposition with the area information registered in the second locationinformation table 331B in order to determine whether or not the secondpresent position is in an area represented by the area information. Ifthe second present position is within an area represented by the areainformation, then the second activation determiner 348B judges that thesecond present position is in the preset location, and outputs anactivation signal. When the second activation determiner 348B comparesthe second present position with area information by way of absolutepositioning, the second activation determiner 348B compares the secondpresent position, which varies from time to time, with fixed areainformation, i.e., the area information by way of absolute positioning.When the second present position enters the area represented by the areainformation, the second activation determiner 348B outputs an activationsignal. When the second activation determiner 348B compares the secondpresent position with area information by way of relative positioning,the second activation determiner 348B compares the second presentposition, which varies from time to time, with area information, whichalso varies from time to time, i.e., the area information by way ofrelative positioning. When the second present position enters the arearepresented by the area information, the second activation determiner348B outputs an activation signal. After having output the activationsignal, if the second activation determiner 348B judges that the secondpresent position has left the area represented by the area informationregistered in the second location information table 331B, then thesecond activation determiner 348B judges that the devices are not withinthe preset location, and outputs a full deactivation signal.

The third activator/deactivator 332C is available in configurationsaccording to three modes, i.e., a first mode, a second mode, and a thirdmode, for example, depending on certain respective conditions.

According to the first mode, the certain condition is that the lineardistance between the devices of the first radiographic image capturingapparatus 10A is equal to or less than a preset reference distance.

As shown in FIG. 17A, the third activator/deactivator 332C according tothe first mode comprises a third present position acquirer 346C, afourth present position acquirer 346D, and a third activation determiner348C.

The third present position acquirer 346C acquires the present position(third present position) of a device, which incorporates therein thebattery controller 306, i.e., the radiation source device 18, thecassette 12, or the like. The fourth present position acquirer 346Dacquires the present position (fourth present position) of a device,which is to be associated with the above device (hereinafter alsoreferred to as the “aforesaid device”). If the linear distance betweenthe third present position and the fourth present position is equal toor smaller than the preset reference distance, then the thirdactivator/deactivator 332C according to the first mode outputs anactivation signal. If the linear distance between the third presentposition and the fourth present position is greater than the presetreference distance, then the third activator/deactivator 332C accordingto the first mode outputs a full deactivation signal.

If the aforesaid device, the present position (third present position)of which is acquired by the third present position acquirer 346C, is theradiation source device 18, then the device to be associated with theabove device refers to the cassette 12. The cassette 12, together withthe radiation source device 18, makes up the first radiographic imagecapturing apparatus 10A.

The third present position acquirer 346C is available in configurationsaccording to two modes, i.e., a first mode and a second mode. Accordingto the first mode, the third present position acquirer 346C detects thethird present position using GPS, and comprises at least a GPS antennaand a GPS receiver. According to the second mode, it is assumed that theoperator 38 uses a car or the like to carry the radiation source device18 and the cassette 12, or carries the radiation source device 18 andthe cassette 12 while also carrying a portable navigation system (mobilephone or the like). The third present position acquirer 346C acquirespositional information from the navigation system as the third presentposition.

The fourth present position acquirer 346D comprises a transfer requestoutput unit 456 and a present position receiver 458. The transferrequest output unit 456 outputs a transfer request signal through thenetwork to the data center. The transfer request signal includes an IDof a device the present position (third present position) of which isacquired by the third present position acquirer 346C, a coderepresentative of a transfer request for information of the presentposition of a device to be associated with the aforesaid device, andinformation representative of the third present position of theaforesaid device. After the data center has received the transferrequest signal from the device, the data center searches a deviceassociation table, not shown, for the ID of a device that corresponds tothe ID included in the transfer request signal, extracts the presentposition of the retrieved ID from the transfer request signal sent fromthe device indicated by the retrieved ID, and transfers the retrieved IDand the present position (fourth present position) of the deviceindicated by the ID via the network to the source of the transferrequest signal. The present position receiver 458 of the fourth presentposition acquirer 346D receives the ID of the device along with thepresent position (fourth present position) thereof, which aretransferred from the data center.

The third activation determiner 348C according to the first modecalculates a difference (linear distance) between the third presentposition (the present position of the device) from the third presentposition acquirer 346C and the fourth present position (the presentposition of the device to be associated with the aforesaid device) fromthe fourth present position acquirer 346D, and determines whether or notthe calculated linear distance is equal to or smaller than a referencedistance registered in the memory 330. If the linear distance is equalto or smaller than the reference distance, then the third activationdeterminer 348C outputs an activation signal. If the linear distance isgreater than the reference distance, then the third activationdeterminer 348C outputs a full deactivation signal.

In other words, the third activator/deactivator 332C according to thefirst mode outputs an activation signal when the linear distance betweenthe radiation source device 18 and the cassette 12 of the firstradiographic image capturing apparatus 10A is equal to or smaller thanthe reference distance. For example, when the radiation source device 18enters a circular area the radius of which is defined by the referencedistance from the cassette 12 at the center of the circular area, thethird activator/deactivator 332C outputs an activation signal.Conversely, when the linear distance between the radiation source device18 and the cassette 12 of the first radiographic image capturingapparatus 10A is greater than the reference distance, e.g., when theradiation source device 18 leaves the circular area the radius of whichis defined by the reference distance from the cassette 12 at the centerof the circular area, the third activator/deactivator 332C outputs afull deactivation signal. The third activator/deactivator 332C willoperate similarly if the radiation source device 18 is at the center ofthe circular area and the cassette 12 enters or leaves the circulararea.

According to the second mode, the certain condition is that the lineardistance between the devices of the first radiographic image capturingapparatus 10A lies within a communication range of each of the devices.

As shown in FIG. 17B, the third activator/deactivator 332C according tothe second mode comprises a request output unit 460, a request receiver462, a responder 464, and a third activation determiner 348C.

The request output unit 460 periodically outputs a request signalincluding the ID of the aforesaid device through a transceiver in awireless fashion.

The request receiver 462 receives a request signal output from anotherdevice through the transceiver.

The responder 464 determines whether or not the ID included in thereceived request signal is equivalent to the ID of a device to beassociated with the aforesaid device, i.e., the ID of a device which,together with the aforesaid device, makes up the first radiographicimage capturing apparatus 10A. If the ID included in the receivedrequest signal is equivalent to the ID of a device to be associated withthe aforesaid device, then the responder 464 outputs an answer signal tothe other device. Since the other device also has a similar responder464, the other device outputs an answer signal in response to a requestsignal output from the aforesaid device.

The third activation determiner 348C according to the second modedetermines whether or not an answer signal has arrived from anotherdevice within a preset response time from when the aforesaid deviceoutput a request signal. If an answer signal has arrived within thepreset response time, then the third activation determiner 348C outputsan activation signal. If an answer signal has not arrived within thepreset response time, then the third activation determiner 348C outputsa full deactivation signal.

Inasmuch as the transceiver 100 of the radiation source device 18 andthe transceiver 94 of the cassette 12 associated with the radiationsource device 18 are energized by the batteries 308 (see FIG. 13), thetransceivers 100, 94 have a small communication range, i.e., from 2 to 5meters, for example, for reducing electric power consumption. When theradiation source device 18 of the first radiographic image capturingapparatus 10A enters the communication range of the cassette 12, forexample, the third activation determiner 348C outputs an activationsignal. Conversely, when the radiation source device 18 leaves thecommunication range of the cassette 12, the third activation determiner348C outputs a full deactivation signal. The third activation determiner348C operates similarly if the cassette 12 enters or leaves thecommunication range of the radiation source device 18.

According to the third mode, the certain condition is that the lineardistance between the devices of the first radiographic image capturingapparatus 10A lies within a range in which the devices can be connectedin a wired or wireless fashion.

As shown in FIG. 17C, the third activator/deactivator 332C according tothe third mode comprises a device connection detector 360 and a thirdactivation determiner 348C.

As shown in FIG. 13, the device connection detector 360 detects whetherthe device, i.e., the radiation source device 18 or the cassette 12, isconnected to at least one of the first energy input/output unit 300 andthe second energy input/output unit 302 in a wired or wireless fashion.A wireless connection is detected by an obstacle sensor such as anultrasonic sensor or the like, which determines whether the device,i.e., the radiation source device 18 or the cassette 12, has enteredinto an area in which the device can be fed wirelessly from the firstenergy input/output unit 300 or the second energy input/output unit 302.When connection of the device to at least one of the first energyinput/output unit 300 and the second energy input/output unit 302 isdetected, the device connection detector 360 outputs a detection signal,which indicates connection of the device to the third activationdeterminer 348C. When connection of the device to either one of thefirst energy input/output unit 300 and the second energy input/outputunit 302 is not detected after the detection signal has been output, thedevice connection detector 360 outputs a non-detection signal to thethird activation determiner 348C.

The third activation determiner 348C according to the third mode outputsan activation signal based on the detection signal input from the deviceconnection detector 360, and outputs a full deactivation signal based onthe non-detection signal input from the device connection detector 360.Wired connection of another device to the aforesaid device indicatesthat the linear distance between the devices makes it possible toconnect them in a wired fashion, whereas wireless connection of anotherdevice to the aforesaid device indicates that the linear distancebetween the devices makes it possible to feed signals to them in awireless fashion.

When it is necessary to refer to the first activation determiner 348A,the second activation determiner 348B, and the third activationdeterminer 348C collectively, they hereinafter will be referred to as an“activation determiner 348.”

If supply timing conditions stored in the memory 330 are free of timingcontrols, then the electric power supply permission instructing unit 350outputs a message indicating permission to supply electric power to themobile terminal 42 and/or energizes (or de-energizes) a pilot lamp (notshown) based on an activation signal input from theactivator/deactivator 332. If the supply timing conditions indicatesupply of electric power before or after capturing of radiographicimages, then the electric power supply permission instructing unit 350outputs a message prompting entry of the image capturing conditions tothe mobile terminal 42, based on the activation signal input from theactivator/deactivator 332.

Based on the activation signal, the electric power supply activator 336is activated. If the supply timing conditions stored in the memory 330are free of timing controls, then the electric power supply activator336 of a device whose electric power supply switch has been operatedactivates the corresponding electric power controller 334 based onoperation of the electric power supply switch. The electric power supplyactivator 336 may activate the electric power controller 334 withoutwaiting for the electric power supply switch to be operated. In such acase, if an interlock process is not performed, then the electric powercontrollers 334 of all the devices outside of the medical organization,all devices in the preset location, or all devices of which the lineardistance therebetween satisfies the certain condition referred to above,are activated, thus tending to cause processing operations to interferewith each other. Therefore, the electric power supply activator 336 ofeach of the devices refers to interlock information registered in thememory 330, i.e., the ID of the radiation source device 18 or thecassette 12 to be used in a preset image capturing process, and only theelectric power supply activator 336 of a device whose ID is identical tothe ID of the interlock information activates the corresponding electricpower controller 334. Thus, for example, only the electric powercontroller 334 of the radiation source device 18 that is used in thepreset image capturing process is operated, while interference from theother devices is prevented.

If the supply timing conditions indicate supply of electric power beforecapturing of radiographic images, then the electric power controller 334is activated based on the image capturing conditions (order) that areinput from the mobile terminal 42. In this case, only the electric powersupply activator 336 of a device having an ID identical to that of theID of the radiation source device 18 or the cassette 12 to be used tocapture radiographic images, which is registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334. If the supply timing conditions indicate supply ofelectric power after capturing of radiographic images, then the electricpower controller 334 is activated based on an image capture completionsignal supplied from an image capture completion determiner 386 (seeFIG. 18). In this case as well, only the electric power supply activator336 of a device having an ID identical to that of the ID of theradiation source device 18 or the cassette 12 to be used to captureradiographic images, which is registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334. The electric power supply activator 336 is shut downbased on a full deactivation signal input from the activator/deactivator332, whereupon the electric power supply activator 336 waits to beactivated at a subsequent time by the activation determiner 348.

The electric power controller 334 is available in differentconfigurations according to two specific examples, i.e., a firstspecific example and a second specific example. According to the firstspecific example, the battery 308 of the radiation source device 18supplies electric power to the battery 308 of the cassette 12, or thebattery 308 of the radiation source device 18 controls supply ofelectric power to the battery 308 of the cassette 12. As shown in FIG.18, the electric power controller 334 according to the first specificexample comprises, as functional components thereof, a device connectiondetector 360, a cassette selector activator 362, a cassette selector364, an integrated supply activator 366, an integrated supply 368, anelectric power supply route setting unit 370, anamount-of-supplied-electric-power setting unit 372, an electric powersupply controller 374, a remaining level detector 376, an image captureinterruption instructing unit 378, a counter 380, a re-supplyinstructing unit 382, an image capture permission instructing unit 384,an image capture completion determiner 386, and an electric power supplycompletion output unit 388. If the activator/deactivator 332 comprisesthe third activator/deactivator 332C (see FIG. 17C) according to thethird mode, then since the device connection detector 360 isincorporated in the third activator/deactivator 332C, the deviceconnection detector 360 is not included within the electric powercontroller 334.

According to the second specific example, the electric power controller334 controls supply of electric power such that the remaining levels ofelectric power stored in the batteries 308 of the connected devices areutilized flexibly between the connected devices, based on preset batterycharging conditions and image capturing conditions. As shown in FIG. 19,the electric power controller 334 according to the second specificexample comprises, in addition to the functional components shown inFIG. 18, an electric power manager 390 and functional componentsancillary to the electric power manager 390, which include a remaininglevel prediction updater 392, a usage history updater 394, a remaininglevel information transfer unit 396, and a usage history transfer unit398. If the activator/deactivator 332 is the third activator/deactivator332C according to the third mode, then since the device connectiondetector 360 already is incorporated in the third activator/deactivator332C, the device connection detector 360 is not included in the electricpower controller 334.

Flexible utilization of the remaining levels of electric power stored inthe batteries 308 between the connected devices implies at least thefollowing aspects:

(1) One or more devices, the batteries of which store an excessiveremaining level of electric power, supply electric power to a devicewhose battery stores a remaining level of electric power that is notsufficient to capture radiographic images.

(2) One or more devices, which are not used to capture radiographicimages, supply electric power required to capture radiographic images tothe aforesaid device, which is used to capture radiographic images.

(3) One or more devices, which are not used to capture radiographicimages, supply electric power required to capture radiographic images tothe aforesaid device, which is used to capture radiographic images,while increasing the remaining level of electric power in the battery ofthe aforesaid device, i.e., the amount of electric power held by theaforesaid device, up to at least a level required to captureradiographic images.

As shown in FIG. 14, the electric power controller 334 limits supply ofelectric power during a period in which the electric power controller334 is supplied with a supply limit signal, which is input thereto fromthe electric power supply limiter 338. Limiting supply of electric powerrefers to stopping supply of electric power, reducing the amount ofelectric power supplied per unit time, or controlling supply of electricpower in a stepwise manner. To stop supply of electric power, as shownin FIG. 13, the electric power controller 334 may output a stop signalto the electric power supply controller 374, thereby causing theelectric power supply controller 374 to control the first through fifthswitchers 314 a through 314 e in order to change to neutral positionsthereof, which are neither input positions nor output positions, forexample. In order to reduce the amount of electric power supplied perunit time, the electric power controller 334 may output asupplied-amount reduction signal to the electric power supply controller374, thereby causing the electric power supply controller 374 to reducethe amount of electric power supplied per unit time to a preset level.In order to control the supply of electric power in a stepwise manner,as described later, the electric power controller 334 may stop supplyingelectric power while electric charges are being stored in the pixels inthe cassette 12 and are converted from analog signals into digitalsignals, supply a small amount of electric power while image data arebeing transferred, and supply a large amount of electric power during anidling period after transferring of the image data is completed. Theelectric power controller 334 stops controlling supply of electric powerbased on a pause signal, which is input from the pause processor 340,and waits to be activated at a subsequent time by the electric powersupply activator 336.

According to the first specific example, as shown in FIG. 20, thecassette selector activator 362 activates the cassette selector 364 whena condition concerning a route, from among battery charging conditionsstored in the memory 330, represents only supply of electric power fromone cassette 12 to the radiation source device 18, the aforesaid deviceis the radiation source device 18, and connection of a plurality ofcassettes 12 to the radiation source device 18 is detected.

The cassette selector 364 comprises a cassette ID acquirer 400, acassette information acquirer 402, and a selector 404.

The cassette ID acquirer 400 sends a transfer request for requestingthat the cassettes 12, which are connected to the radiation sourcedevice 18, transfer IDs thereof. The cassettes 12 output IDs to theradiation source device 18 based on the transfer request. The cassetteID acquirer 400 acquires the IDs and stores the IDs in the memory 330.

The cassette information acquirer 402 acquires cassette informationtables, which contain information concerning defective pixels, etc., andusage history tables corresponding to the acquired IDs via the network.

The selector 404 selects a cassette 12 that matches selecting conditionsfrom among the connected cassettes 12 based on the selecting conditions,the acquired cassette information tables, and the acquired usage historytables, which are stored in the memory 330. The selector 404 thenoutputs the ID of the selected cassette 12 to the electric power supplyroute setting unit 370.

The selecting conditions for selecting a cassette 12 include:

(1-a) a large-size cassette 12;

This condition serves the purpose of discharging electric power from alarge-size cassette 12 in a special environment where no large-sizecassette 12 is used. The size of a cassette 12 is determined based onsize information that is recorded in the cassette information table.

(1-b) a small-size cassette 12;

This condition serves the purpose of preferentially discharging electricpower from a cassette 12 that is less versatile.

(1-c) a cassette 12 with many defective pixels;

This condition serves the purpose of preferentially discharging electricpower from a cassette 12 that is less frequently used, therebypreventing the cassette 12 from becoming disabled substantiallysimultaneously. The number of defective pixels is determined based oninformation concerning defective pixels recorded in the cassetteinformation table. The information concerning defective pixels, which isrecorded in the cassette information table, is regularly or irregularlyupdated upon calibration or the like, for example.

(1-d) a cassette 12 with a small imaging area;

The size of an imaging area is calculated from information concerningdefective pixels, which is recorded in the cassette information table,particularly positional information about the defective pixels.

(1-e) a cassette 12 with a highly deteriorated battery 308;

The level of deterioration of the battery 308 is determined based on thenumber of times that the cassette 12 has been used, which is recorded inthe cassette information table.

(1-f) a cassette 12 with a lowly deteriorated battery 308;

(1-g) a cassette 12 that has been used many times;

The number of times that the cassette 12 has been used is determinedbased on a counted number of times that the cassette 12 has been used,which is recorded in the cassette information table, or based oninformation concerning an accumulated radiation dose, which is recordedin the cassette information table.

(1-h) a cassette 12 with a small remaining built-in memory capacity;

The remaining built-in memory capacity is determined based on a reply,which is sent from the cassette controller 92 in response to an inquiryas to the remaining built-in memory capacity sent to the cassettecontroller 92.

(1-i) a cassette 12 that is positioned a small distance from theradiation source device 18;

This condition serves the purpose of selecting a cassette 12 that caneasily supply electric power over a small distance, thereby reducing theburden on the circuits involved. The distance from the radiation sourcedevice 18 to the cassette 12 is determined based on the informationconcerning present positions of the cassettes 12 acquired via GPS, ordistance information from a range sensor such as an ultrasonic sensor, athree-dimensional magnetic sensor, or the like.

As shown in FIG. 21, the integrated supply activator 366 activates theintegrated supply 368 when a condition concerning a route, from amongthe battery charging conditions stored in the memory 330, representsonly supply of electric power from a plurality of cassettes 12 to theradiation source device 18, the aforesaid device is the radiation sourcedevice 18, and connection of a plurality of cassettes 12 to theradiation source device 18 is detected.

The integrated supply 368 comprises a cassette ID acquirer 400, acassette information acquirer 402, and a weighting setting unit 406.

The cassette ID acquirer 400 sends a transfer request for requestingthat cassettes 12 connected to the radiation source device 18 transferIDs thereof. The cassettes 12 output IDs to the radiation source device18 based on the transfer request. The cassette ID acquirer 400 acquiresthe IDs and stores the IDs in the memory 330.

The cassette information acquirer 402 acquires cassette informationtables, which contain information concerning defective pixels, etc., andusage history tables corresponding to the acquired IDs via the network.

The weighting setting unit 406 sets weighting coefficients forrespective amounts of electric power to be supplied from the cassettes12 to the radiation source device 18, based on integrating conditions,the acquired cassette information tables, and the acquired usage historytables, which are stored in the memory 330. The weighting setting unit406 then outputs the set weighting coefficients, together withcorresponding ID information, to the amount-of-supplied-electric-powersetting unit 372.

The integrating conditions include:

(2-a) The amount of supplied electric power is sorted depending on theamount of defective pixels;

As the number of defective pixels becomes greater, the weighting settingunit 406 sets a weighting coefficient for increasing the amount ofsupplied electric power. Conversely, as the number of defective pixelsbecomes smaller, the weighting setting unit 406 sets a weightingcoefficient for reducing the amount of supplied electric power.

(2-b) The amount of supplied electric power is sorted depending on theimaging area;

As the imaging area becomes smaller, the weighting setting unit 406 setsa weighting coefficient for increasing the amount of supplied electricpower. Conversely, as the imaging area becomes greater, the weightingsetting unit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

(2-c) The amount of supplied electric power is sorted depending on thelevel of deterioration of the battery 308;

As the level of deterioration of the battery 308 becomes greater, theweighting setting unit 406 sets a weighting coefficient for increasingthe amount of supplied electric power. Conversely, as the level ofdeterioration of the battery 308 becomes smaller, the weighting settingunit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

(2-d) The amount of supplied electric power is sorted depending on thenumber of times that the cassette 12 has been used;

As the number of times that the cassette 12 has been used becomesgreater, the weighting setting unit 406 sets a weighting coefficient forincreasing the amount of supplied electric power. Conversely, as thenumber of times that the cassette 12 has been used is smaller, theweighting setting unit 406 sets a weighting coefficient for reducing theamount of supplied electric power.

(2-e) The amount of supplied electric power is sorted depending on theremaining built-in memory capacity;

As the amount of supplied electric power becomes smaller, the weightingsetting unit 406 sets a weighting coefficient for increasing the amountof supplied electric power. Conversely, as the amount of suppliedelectric power becomes greater, the weighting setting unit 406 sets aweighting coefficient for reducing the amount of supplied electricpower.

(2-f) The amount of supplied electric power is sorted depending on thedistance to the radiation source device 18.

As the distance to the radiation source device 18 becomes smaller, theweighting setting unit 406 sets a weighting coefficient for increasingthe amount of supplied electric power. Conversely, as the distance tothe radiation source device 18 becomes greater, the weighting settingunit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

Then, the electric power supply route setting unit 370 sets a route forsupply of electric power based on a condition concerning the route fromamong the battery charging conditions stored in the memory 330. Forexample, the electric power supply route setting unit 370 sets a routefrom the radiation source device 18 to the cassette 12, or a route fromthe cassette 12 to the radiation source device 18. If the electric powersupply route setting unit 370 is supplied with an ID from the cassetteselector 364, then the electric power supply route setting unit 370 setsa route from the cassette 12 to the radiation source device 18corresponding to the ID. If the electric power supply route setting unit370 is supplied with a plurality of IDs from the integrated supply 368,then the electric power supply route setting unit 370 sets routes fromthe cassettes 12 to the radiation source device 18 corresponding to suchIDs. Route information representing the set IDs is displayed on adisplay screen of the mobile terminal 42. The condition concerning theroute is descriptive of at least one source of electric power. If thesource of electric power is the radiation source device 18, then theradiation source device 18 supplies electric power to the cassette 12.If the source of electric power is the cassette 12, then the cassette 12supplies electric power to the radiation source device 18. The conditionconcerning the route can be changed as desired by the mobile terminal42. If the re-supply instructing unit 382 provides a re-supplyinstruction, i.e., if the re-supply instructing unit 382 inputs are-supply instruction signal to the electric power supply route settingunit 370, then the electric power supply route setting unit 370 sets theroute for supply of electric power based on battery charging conditions.If the operator 38 intends to additionally charge the battery of anotherdevice, e.g., the radiation source device 18 or the cassette 12, thenthe operator 38 enters the route for supply of electric power to theother device, i.e., a route from the other device to the radiationsource device 18 or the cassette 12 that is used to capture radiographicimages, or a route from the radiation source device 18 or the cassette12 that is used to capture radiographic images to the other device, andalso enters an amount of electric power to be supplied. Based on theentered route for supply of electric power, the electric power supplyroute setting unit 370 outputs a supply source instruction signal or asupply destination instruction signal to the electric power supplycontroller 374 of each device.

The amount-of-supplied-electric-power setting unit 372 sets an amount ofelectric power to be supplied based on a condition concerning the amountof electric power to be supplied, from among the battery chargingconditions. At least items such as a full battery charge, an amount ofelectric power to be supplied that is required to capture a singleradiographic image, etc., can be used as conditions concerning theamount of electric power to be supplied. One of such items, which isselected at present, is applicable as the condition concerning theamount of electric power to be supplied. An item to be applied can beselected as desired by the mobile terminal 42. An amount of electricpower to be supplied can be set as a numerical value by the mobileterminal 42. If the amount-of-supplied-electric-power setting unit 372is supplied with a plurality of IDs and corresponding coefficients fromthe integrated supply 368, then the amount-of-supplied-electric-powersetting unit 372 multiplies the amount of electric power to be suppliedby such coefficients in order to set amounts of electric power to besupplied respectively from the cassettes 12 to the radiation sourcedevice 18. If the re-supply instructing unit 382 provides a re-supplyinstruction, then the amount-of-supplied-electric-power setting unit 372sets an amount of electric power to be supplied based on a conditionconcerning the amount of electric power to be supplied, from among thebattery charging conditions. The amount of electric power to be suppliedcan also be changed as desired by the mobile terminal 42. If batteriesof devices are to be charged as well, then theamount-of-supplied-electric-power setting unit 372 also sets respectiveamounts of electric power to be supplied in order to charge thebatteries, and supplies the set amounts of electric power to be suppliedto the electric power supply controllers 374 of each of the respectivedevices.

As shown in FIG. 13, if a supply source instruction signal is input tothe electric power supply controller 374, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. If a supply destination instruction signal is input to theelectric power supply controller 374, then the electric power supplycontroller 374 controls the battery 308 in order to receive electricpower. Based on a remaining level of electric power in the battery 308,which is detected by the remaining level detector 376, the electricpower supply controller 374 controls the battery 308 that is suppliedwith electric power at a constant charging rate, or controls the battery308 to supply electric power at the constant discharging rate. Assumingthat the amount of electric power to be supplied is small, then theelectric power supply controller 374 can quickly charge or discharge thebattery 308. If the remaining level of electric power in the battery308, which is detected by the remaining level detector 376, isinsufficient to capture a single radiographic image, then the electricpower supply controller 374 outputs an imaging disable signal, whichincludes the remaining level of electric power and the ID of theaforesaid device. When the supply of electric power to the battery 308or the supply of electric power from the battery 308 is completed, theelectric power supply controller 374 outputs a supply terminationsignal.

As described above, the remaining level detector 376 detects a remaininglevel of electric power in the battery 308, and sends a signalrepresentative of the detected remaining level of electric power in thebattery 308 to the electric power supply controller 374.

The image capture interruption instructing unit 378, as shown in FIG.18, outputs a message representing interruption of an image capturingprocess to the mobile terminal 42, based on an imaging disabled signalinput from the electric power supply controller 374.

The counter 380 counts the number of times that the exposure switch 48has been turned on. The counter 380 resets the count (count=0) based onan image capture completion signal, which is input from the imagecapture completion determiner 386.

Based on the imaging disabled signal input from the electric powersupply controller 374, the re-supply instructing unit 382 outputs are-supply instruction signal including the preset count of the counter380, the amount of electric power included in the imaging disabledsignal, and the ID of the aforesaid device, respectively, to theelectric power supply route setting unit 370, theamount-of-supplied-electric-power setting unit 372, and the electricpower manager 390. If electric power is supplied after capturing ofradiographic images, since the electric power controller 334 itself isnot activated, the re-supply instructing unit 382 of the radiationsource device 18 or the cassette 12 that is used to capture radiographicimages activates the electric power supply route setting unit 370, theamount-of-supplied-electric-power setting unit 372, and the electricpower manager 390, using an interrupt routine for emergency.

If the supply timing conditions recorded in the memory 330 are free oftiming controls, or indicate supply electric power before capturing ofradiographic images, then the image capture permission instructing unit384 outputs an image capture permission message to the mobile terminal42 based on supply termination signals, which are input from theelectric power supply controllers 374 of all of the devices to whichelectric power is supplied.

The image capture completion determiner 386 compares the number of timesthat radiographic images have been captured in the image capturingconditions with the count of the counter 380, and outputs an imagecapture completion signal when the number of times that radiographicimages have been captured becomes equal to the count.

The electric power supply completion output unit 388 outputs an electricpower supply completion signal based on supply termination signals,which are input from the electric power supply controllers 374 of all ofthe devices to which electric power is supplied.

The electric power supply limiter 338 shown in FIG. 14 determineswhether or not a radiographic image of the subject 50 is being capturedif the supply timing conditions recorded in the memory 330 include acondition indicating that “the supply of electric power is stopped whilea radiographic image is being captured.” If a radiographic image isbeing captured, then the electric power supply limiter 338 outputs asupply limit signal during the period in which a radiographic image isbeing captured. More specifically, when the exposure switch 48 is turnedon, the electric power supply limiter 338 outputs a supply limit signal.Thereafter, when a predetermined period of time has elapsed, theelectric power supply limiter 338 stops outputting the supply limitsignal. The electric power controller 334 limits supply of electricpower during the period in which the supply limit signal is inputthereto.

The period during which the electric power supply limiter 338 outputsthe supply limit signal should preferably be any one of a period(storage period) in which radiation 46 having passed through the subject50 is applied to the radiation detector 86 and converted by ascintillator (not shown) into visible light, and the visible light isconverted at each pixel 132 into electric signals that are stored aselectric charges (signal charges), a period (reading period) duringwhich the stored electric charges are read, and a period(analog-to-digital conversion period) during which the read electriccharges (analog signals) are converted into digital signals by the A/Dconverter 154, a period which is a combination of the above periods, ora period that includes all the above periods. In the above threeperiods, the image signals (radiographic image information) are highlysusceptible to noise. More specifically, in the storage period and thereading period, since the level of electric charge is very low, theradiographic image information is highly susceptible to noise. In theanalog-to-digital conversion period, analog signals are less resistantto noise than digital signals, and any noise added to the analog signalstends to be converted into digital signals and appear in the image data.

The storage period includes a period during which the radiation source44 emits radiation 46. More specifically, after the storage period hasstarted, the radiation source 44 begins to emit radiation 46 as quicklyas possible, and after the radiation source 44 has stopped emittingradiation 46, the stored electric charges are read immediately from thepixels. Any time lag associated with these processes should be reducedas much as possible in order to reduce dark current, and hence increasethe quality of radiographic images that are generated. The readingperiod refers to a period during which the TFTs 140 are turned on, andsignals are supplied through the amplifiers 148 to the A/D converter154. The reading period and the analog-to-digital conversion periodoccur substantially at the same time, although the reading time startsslightly earlier than the analog-to-digital conversion period.

The period during which the supply limit signal is output should extendfrom a time when the supply limit signal is output to a time when theradiation source device 18 stops emitting radiation 46, or morepreferably reside within the period during which the radiographic imageis captured, so that the cassette 12 can detect radiation 46 with highquality. A predicted time, which is required to capture and display aradiographic image, may be preset and used as the period during whichthe supply limit signal is output. The degree to which the amount ofsupplied electric power is reduced per unit time may be setexperimentally to a value for preventing noise from being added to theradiographic image, or for reducing any added noise to a level that isnot detrimental to the quality of the radiographic image.

If the supply timing conditions recorded in the memory 330 are free oftiming controls, or indicate supply of electric power before capturingof radiographic images, then the pause processor 340 shown in FIG. 14outputs a pause signal to the electric power controller 334, based on animage capture completion signal input from an image capture completiondeterminer 386. If the supply timing conditions recorded in the memory330 indicate supply of electric power after capturing of radiographicimages, then the pause processor 340 outputs a pause signal to theelectric power controller 334, based on an electric power supplycompletion signal input from the electric power supply completion outputunit 388.

According to the second specific example, the electric power manager 390shown in FIG. 19 gives the electric power supply controller 374information for controlling supply of electric power, such that theremaining levels of electric power stored in the batteries 308 of thedevices are utilized flexibly between the devices, based on presetbattery charging conditions and image capturing conditions. The electricpower manager 390 is incorporated in the radiation source device 18and/or the cassette 12. As shown in FIG. 22, the electric power manager390 comprises an ID acquirer 410, an information acquirer 412 foracquiring various information, an amount-of-consumed-electric-powerpredictor 414, and an information updater 416.

The ID acquirer 410 sends a transfer request for requesting the devicethat incorporates the electric power manager 390 therein and anotherdevice that is connected to the device to transfer respective IDsthereof. Based on the transfer request, the devices output their IDsrespectively to the electric power manager 390. The ID acquirer 410acquires the IDs input thereto and registers the acquired IDs in thememory 330. If another radiation source device 18 or another cassette12, in addition to the radiation source device 18 and the cassette 12used to capture radiographic images, are connected or are present in anarea in which they can be fed wirelessly, then the ID acquirer 410 alsoacquires IDs of the other radiation source device 18 and the cassette12.

The information acquirer 412 for acquiring various information acquirespresent or previous image capturing conditions, which are input via themobile terminal 42 or the network, remaining level-of-electric-energyinformation tables corresponding to the IDs, previous image capturingconditions corresponding to the IDs, and usage history tablescorresponding to the IDs, and stores such information in the memory 330.

The amount-of-consumed-electric-power predictor 414 calculates amountsof electric power that are consumed by the radiation source device 18and the cassette 12 used to capture radiographic images, from thebattery charging conditions stored in the memory 330 and the present orprevious image capturing conditions representative of the number ofradiographic images to be captured, mAs values, etc. Theamount-of-consumed-electric-power predictor 414 then corrects thecalculated amounts of electric power by multiplying the calculatedamounts by usage histories of the radiation source device 18 and thecassette 12, i.e., coefficients corresponding to the number of timesthat the radiation source device 18 and the cassette 12 have been used,thereby predicting amounts of electric power that will be consumed bythe radiation source device 18 and the cassette 12 during the presentimage capturing process, or amounts of electric power consumed by theradiation source device 18 and the cassette 12 in the previous imagecapturing process. If a re-supply instruction is input from there-supply instructing unit 382, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power to be consumed by the respective devices indicated by theIDs, i.e., the radiation source device 18 and the cassette 12 to bere-supplied with electric power, from image capturing conditions for theimage capturing process to be carried out, from which image capturingconditions for radiographic images already captured (indicated by thecount) are excluded, which are among the present image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc., and corrects the calculated amounts ofelectric power by multiplying the calculated amounts by usage historiesof the radiation source device 18 and the cassette 12, i.e.,coefficients corresponding to the number of times that the radiationsource device 18 and the cassette 12 have been used, thereby predictingamounts of electric power that will be consumed by the devices of theIDs in the image capturing process to be carried out.

The information updater 416 subtracts the amount of supplied electricpower from the remaining level of electric power of a device serving asan electric power supply source, and adds the amount of suppliedelectric power to the remaining level of electric power of a device thatserves as an electric power supply destination, in the remaininglevel-of-electric-energy information table. If the re-supply instructingunit 382 outputs a re-supply instruction, then the information updater416 changes only the remaining levels of electric power of therespective devices indicated by the IDs. A value produced by adding thepresent amount of supplied electric power to the amount of electricpower included in the re-supply instruction signal is recorded in thememory 330. Since this value reflects the amount of electric power fromthe electric power supply controller 374, an error in the remaininglevel of electric power, which is represented by only a predicted value,is corrected.

According to the second specific example, because the electric powercontroller 334 includes the electric power manager 390, the electricpower supply route setting unit 370 and theamount-of-supplied-electric-power setting unit 372 operate differentlyfrom those of the electric power controller 334 according to the firstspecific example.

More specifically, the electric power supply route setting unit 370according to the second specific example sets a route for supply ofelectric power based on the predicted amount of electric power, and theremaining levels of electric power in the batteries 308 of the radiationsource device 18 and the cassette 12 (remaining level-of-electric-energyinformation tables). Typically, the electric power supply route settingunit 370 sets a route for supplying electric power to a device, thebattery of which stores a remaining level of electric power that willalmost be eliminated in the present image capturing process. Informationconcerning the set route is displayed on the display screen of themobile terminal 42. If the re-supply instructing unit 382 outputs are-supply instruction, then the electric power supply route setting unit370 sets routes for supplying electric power to respective devicesindicated by the IDs. If the operator 38 intends to supply electricpower additionally from other devices, i.e., a radiation source device18 and a cassette 12 that are not used to capture radiographic images,then the operator 38 enters routes for supplying electric power, andamounts of electric power, from the other devices, i.e., routes forsupplying electric power from the other devices to the respectivedevices indicated by the IDs. If the operator 38 additionally intends tocharge a battery using another device, i.e., a radiation source device18 or a cassette 12, then the operator 38 enters a route for supplyingelectric power to or from the other device, i.e., a route from the otherdevice to the radiation source device 18 or the cassette 12 that is usedto capture radiographic images, or a route from the radiation sourcedevice 18 or the cassette 12 that is used to capture radiographic imagesto the other device, together with the amount of electric power to besupplied, and an order in which such electric power is supplied. Basedon the entered route for supplying electric power, the electric powersupply route setting unit 370 outputs a supply source instruction signalor a supply destination instruction signal to the electric power supplycontroller 374 of each of the devices.

The amount-of-supplied-electric-power setting unit 372 according to thesecond specific example sets the supplied amount of electric power basedon the predicted amount of electric power and the remaining levels ofelectric power in the batteries 308 of the radiation source device 18and the cassette 12 (remaining level-of-electric-energy informationtables). Thus, at most, the predicted amount of electric power issupplied to a device, the battery of which stores a remaining level ofelectric power, which will almost be eliminated during the present imagecapturing process. The amount of electric power, which is supplied tosuch a device, may be one-half or one-third the predicted amount ofelectric power. The information concerning the set amount of electricpower is displayed on a display screen of the mobile terminal 42. Theset amount of electric power can also be changed as desired by themobile terminal 42. If the operator 38 additionally intends to charge abattery, then the amount-of-supplied-electric-power setting unit 372also sets the amount of electric power to be supplied, so as toadditionally charge the battery. The amount of electric power predictedbased on previous image capturing conditions is supplied in order tosupplement the amount of electric power consumed in the previous imagecapturing process. If the re-supply instructing unit 382 outputs are-supply instruction, then the amount-of-supplied-electric-powersetting unit 372 sets the amount of electric power to equal thepredicted amount of electric power. The set amount of electric power canbe changed as desired by the mobile terminal 42. If the operator 38additionally intends to charge a battery, then theamount-of-supplied-electric-power setting unit 372 also sets an amountof electric power to be supplied, so as to additionally charge thebattery. The set amount of electric power then is supplied to theelectric power supply controller 374 of the corresponding device.

Among functional components that are ancillary to the electric powermanager 390, the remaining level prediction updater 392 shown in FIG. 19functions, assuming that the supply timing conditions recorded in thememory 330 indicate supply of electric power before capturing ofradiographic images. Each time that the operator 38 turns on theexposure switch 48, the remaining level prediction updater 392 updates,by way of subtraction, the remaining levels of electric power stored inthe batteries that are recorded in the remaininglevel-of-electric-energy information tables, i.e., the remaining levelsof electric power stored in the batteries 308 of the radiation sourcedevice 18 and the cassette 12, which are used to capture radiographicimages. More specifically, with respect to the radiation source device18 and the cassette 12, the remaining level prediction updater 392calculates amounts of electric power consumed in order to captureradiographic images based on the image capturing conditions and theusage history tables, and subtracts the calculated amounts of electricpower from the remaining levels of electric power stored in thebatteries 308 of the radiation source device 18 and the cassette 12,which are recorded in the remaining level-of-electric-energy informationtables.

The usage history updater 394 adds to the usage counts recorded in theusage history tables the number of times that the exposure switch 48 hasbeen turned on, i.e., the number of times that the radiation sourcedevice 18 and the cassette 12 have been used.

If the supply timing conditions recorded in the memory 330 indicatesupply of electric power before capturing of radiographic images, thenthe remaining level information transfer unit 396 shown in FIG. 19transfers the remaining level-of-electric-energy information tables viathe network to the database of a data center, such as a medicalorganization or the like for updating, based on an image capturecompletion signal input from the image capture completion determiner386. If the supply timing conditions recorded in the memory 330 indicatesupply of electric power after capturing of radiographic images, thenthe remaining level information transfer unit 396 transfers theremaining level-of-electric-energy information tables via the network tothe database of the data center for updating, based on an electric powersupply completion signal input from the electric power supply completionoutput unit 388.

If the supply timing conditions recorded in the memory 330 indicatesupply of electric power before capturing of radiographic images, thenthe usage history transfer unit 398 transfers the usage history tablesvia the network to the database of the data center for updating, basedon an image capture completion signal input from the image capturecompletion determiner 386. If the supply timing conditions recorded inthe memory 330 indicate supply of electric power after capturing ofradiographic images, then the usage history transfer unit 398 transfersthe usage history tables via the network to the database of the datacenter for updating, based on an electric power supply completion signalinput from the electric power supply completion output unit 388.

The first radiographic image capturing apparatus 10A basically isconstructed as described above. Operations of the first radiographicimage capturing apparatus 10A will be described below with reference tothe flowcharts shown in FIGS. 23 through 29.

First, an operation sequence of the first radiographic image capturingapparatus 10A, if the supply timing conditions are free of timingcontrols, will be described below with reference to the flowcharts shownin FIGS. 23 and 24.

In step S1 shown in FIG. 23, the activator/deactivator 332 performs adetermining process. More specifically, if the activator/deactivator 332is the first activator/deactivator 332A (see FIGS. 15A and 15B), thenthe first activator/deactivator 332A determines whether or not the firstpresent position is outside of a medical organization. If the operator38 carries the first radiographic image capturing apparatus 10A, thedevices of which are coupled together, out of the medical organizationwhile gripping the grip 24, then control proceeds to step S2, duringwhich the first activator/deactivator 332A outputs an activation signal.

If the activator/deactivator 332 is the second activator/deactivator332B (see FIGS. 16A and 16B), then the second activator/deactivator 332Bdetermines whether or not the second present position is in a presetlocation, i.e., at the location indicated by the area informationregistered in the second location information table 331B, such as amedical organization, an accident site, a disaster site, a medicalcheckup site, a home-care service site, or a transport vehicle such asan ambulance, a mobile medical checkup motor vehicle, a railway car, aship, an aircraft, or the like. If the operator 38 carries the firstradiographic image capturing apparatus 10A, the devices of which arecoupled together, into the preset location while gripping the grip 24,then control proceeds to step S2, during which the secondactivator/deactivator 332B outputs an activation signal.

If the activator/deactivator 332 is the third activator/deactivator 332C(see FIGS. 17A through 17C), then the third activator/deactivator 332Cdetermines whether or not the distance between the aforesaid device andanother device satisfies a certain condition. More specifically, thethird activator/deactivator 332C according to the first mode (see FIG.17A) determines whether or not the linear distance between the thirdpresent position (the aforesaid device) and the fourth present position(another device) is equal to or smaller than a preset referencedistance. The third activator/deactivator 332C according to the secondmode (see FIG. 17B) determines whether or not an answer signal hasarrived from the other device within a preset response time from whenthe aforesaid device outputs a request signal, i.e., whether thedistance between the devices is within the communication range of eachof the devices. The third activator/deactivator 332C according to thethird mode (see FIG. 17C) determines whether or not a device (theradiation source device 18 or the cassette 12) is connected to at leastone of the first energy input/output unit 300 and the second energyinput/output unit 302 in a wired fashion or a wireless fashion, i.e.,whether the distance between the devices is sufficient for the devicesto be connected in a wired fashion, or whether the distance between thedevices allows them to be fed wirelessly.

When the operator 38 approaches the radiation source device 18 and thecassette 12 of the first radiographic image capturing apparatus 10Atoward one another until the linear distance between such devices isequal to or smaller than the reference distance, when the distancebetween the devices enters within the communication range, or when thedistance between the devices allows the devices to be connected in awired fashion or wireless fashion, then the third activator/deactivator332C outputs an activation signal in step S2.

Thereafter, in step S3, the electric power supply permission instructingunit 350 outputs a message indicating permission to supply electricpower to the mobile terminal 42 and/or to energize (de-energize) thepilot lamp.

In step S4, the electric power controller 334 is activated based onoperation of the electric power supply switch. The electric power supplyactivator 336 may also activate the electric power controller 334without waiting for operation of the electric power supply switch. Atthis time, the electric power supply activator 336 of each of thedevices refers to interlock information registered in the memory 330,i.e., an ID of the radiation source device 18 or the cassette 12 that isused in a preset image capturing process, and only the electric powersupply activator 336 of the device having an ID is identical to that ofthe interlock information activates the corresponding electric powercontroller 334.

In step S5, the device connection detector 360 detects whether or notthe device, i.e., the radiation source device 18 or the cassette 12, isconnected to the first energy input/output unit 300 or to the secondenergy input/output unit 302. If the activator/deactivator 332 is thethird activator/deactivator 332C (see FIG. 17C), then since the deviceconnection detector 360 has already detected connection thereof in stepS1, control proceeds from step S4 to step S6, while skipping step S5.

After the device connection detector 360 has detected the connection instep S5, the cassette selector activator 362 determines whether or notconditions are satisfied for activating the cassette selector 364 instep S6. More specifically, the cassette selector activator 362activates the cassette selector 364 when a condition concerning a route,from among the battery charging conditions stored in the memory 330,represents only supply of electric power from one cassette 12 to theradiation source device 18, the aforesaid device is the radiation sourcedevice 18, and connection of a plurality of cassettes 12 to theradiation source device 18 is detected.

In step S7, the cassette selector 364 selects a cassette 12 that matchesthe selecting conditions from among the connected cassettes 12, based ona plurality of IDs that are acquired by the cassette ID acquirer 400,selecting conditions stored in the memory 330, and the cassetteinformation tables and the usage history tables, which are acquired bythe cassette information acquirer 402. The cassette selector 364 thenoutputs the ID of the selected cassette 12 to the electric power supplyroute setting unit 370.

After step S7, or if the cassette selector activator 362 judges thatconditions are not satisfied for activating the cassette selector 364 instep S6, control proceeds to step S8, during which the integrated supplyactivator 366 determines whether conditions are not satisfied in orderto activate the integrated supply 368. More specifically, the integratedsupply activator 366 activates the integrated supply 368 when acondition concerning a route, from among the battery charging conditionsstored in the memory 330, represents only supply of electric power froma plurality of cassettes 12 to the radiation source device 18, theaforesaid device is the radiation source device 18, and connection of aplurality of cassettes 12 to the radiation source device 18 is detected.

In step S9, the integrated supply 368 sets weighting coefficients forthe amounts of electric power to be supplied from the cassettes 12 tothe radiation source device 18 based on a plurality of IDs that areacquired by the cassette ID acquirer 400, integrating conditions storedin the memory 330, the cassette information tables, and the usagehistory tables, which are acquired by the cassette information acquirer402. The integrated supply 368 then outputs the set weightingcoefficients to the corresponding amount-of-supplied-electric-powersetting unit 372.

After step S9, or if the integrated supply activator 366 judges thatconditions are not satisfied for activating the integrated supply 368 instep S8, then control proceeds to step S10, during which the electricpower supply route setting unit 370 sets a route for supply of electricpower, based on conditions concerning the route from among the batterycharging conditions stored in the memory 330. For example, the electricpower supply route setting unit 370 sets a route from the radiationsource device 18 to the cassette 12, or a route from the cassette 12 tothe radiation source device 18. If the electric power supply routesetting unit 370 is supplied with an ID from the cassette selector 364,then the electric power supply route setting unit 370 sets a route fromthe cassette 12 identified by the ID to the radiation source device 18.If the electric power supply route setting unit 370 is supplied with aplurality of IDs from the integrated supply 368, then the electric powersupply route setting unit 370 sets multiple routes from the cassettes 12identified by the IDs to the radiation source device 18. Thereafter, theelectric power supply route setting unit 370 outputs informationconcerning the set route (route information) to the electric powersupply controller 374. More specifically, based on the set route forsupply of electric power, the electric power supply route setting unit370 outputs a supply source instruction signal, or a supply destinationinstruction signal, to the electric power supply controller 374 of eachdevice. For example, it is assumed that the first energy input/outputunit 300 of the radiation source device 18 is connected to the firstenergy input/output unit 300 of the cassette 12. If the set route is aroute for supplying electric power from the radiation source device 18to the cassette 12, then the electric power supply route setting unit370 outputs a supply source instruction signal to the electric powersupply controller 374 of the radiation source device 18, and furtheroutputs a supply destination instruction signal to the electric powersupply controller 374 of the cassette 12. If the set route is a routefor supplying electric power from the cassette 12 to the radiationsource device 18, then the electric power supply route setting unit 370outputs a supply destination instruction signal to the electric powersupply controller 374 of the radiation source device 18, and furtheroutputs a supply source instruction signal to the electric power supplycontroller 374 of the cassette 12.

In step S11, the amount-of-supplied-electric-power setting unit 372 setsan amount of electric power to be supplied (supplied amount of electricpower) based on a condition concerning the amount of electric power tobe supplied, from among the battery charging conditions. For example,the amount-of-supplied-electric-power setting unit 372 sets an amount ofelectric power to be supplied for a full battery charge, or forcapturing a single radiographic image. If theamount-of-supplied-electric-power setting unit 372 is supplied with aplurality of IDs and corresponding coefficients from the integratedsupply 368, then the amount-of-supplied-electric-power setting unit 372multiplies the amount of electric power to be supplied by suchcoefficients in order to set respective amounts of electric power to besupplied to the radiation source device 18 from the respective cassettes12. The amount-of-supplied-electric-power setting unit 372 outputsinformation concerning the set amounts of electric power to be suppliedto the electric power supply controllers 374 of the correspondingdevices.

In step S12, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. Further, if the electric power supply controller 374 is suppliedwith a supply destination instruction signal, then the electric powersupply controller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308 orsupply of electric power from the battery 308 is completed, then theelectric power supply controller 374 outputs a supply terminationsignal.

In step S13, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals, which are input from the electric power supplycontrollers 374 of all of the devices to which electric power has beensupplied.

In step S14, the image capture permission instructing unit 384 outputs amessage representative of permission to capture an image to the mobileterminal 42, based on the electric power supply completion signal inputfrom the electric power supply completion output unit 388.

In step S15, the operator 38 prepares the first radiographic imagecapturing apparatus 10A for capturing radiographic images at a sitewhere the first radiographic image capturing apparatus 10A has beencarried. This preparatory procedure has been described in detail above,and will not be described below.

When the subject 50 is positioned during the preparatory procedure,control proceeds to step S16 shown in FIG. 24, in which the operator 38turns on the exposure switch 48 to begin capturing radiographic imagesof the subject 50. At this time, the counter 380 updates the count byincrementing the count by +1.

When the operator 38 turns on the exposure switch 48 in step S16, thenin step S17, the electric power supply limiter 338 outputs a supplylimit signal to the electric power controller 334 during theaforementioned period. During the period in which the electric powercontroller 334 is supplied with the supply limit signal, the electricpower controller 334 temporarily interrupts the operation thereof tosupply electric power.

In step S18, the electric power controller 334 determines whether or notelectric power needs to be re-supplied, based on whether the electricpower supply controller 374 of any device has output an imaging disabledsignal. More specifically, if the remaining level of electric powerstored in the battery 308 of the radiation source device 18 or thecassette 12 is insufficient to capture a single radiographic image, thenthe electric power supply controller 374 outputs an imaging disabledsignal, including the remaining level of electric power and the ID ofthe aforesaid device to the re-supply instructing unit 382, for therebyrequesting the re-supply instructing unit 382 to re-supply electricpower.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S19, in which the imagecapture interruption instructing unit 378 outputs a message indicatinginterruption of image capturing to the mobile terminal 42. The mobileterminal 42 displays a message on a display screen thereof, andpreferably outputs an alarm sound, for prompting the operator 38 tointerrupt the image capturing process.

Thereafter, in step S20, the re-supply instructing unit 382 outputs are-supply instruction signal to the electric power supply route settingunit 370, as well as to the amount-of-supplied-electric-power settingunit 372.

In step S21, the electric power supply route setting unit 370 sets aroute for re-supplying electric power (re-supply route) based on thebattery charging conditions, and based on the set re-supply route,outputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachdevice.

In step S22, the amount-of-supplied-electric-power setting unit 372 setsan amount of electric power to be re-supplied (amount of re-suppliedelectric power) based on a condition concerning the supplied amount,from among the battery charging conditions, and outputs informationconcerning the set amount of re-supplied electric power to the electricpower supply controller 374 of the corresponding device.

In step S23, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. Further, if the electric power supply controller 374 is suppliedwith a supply destination instruction signal, then the electric powersupply controller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308, orsupply of electric power from the battery 308 is completed, the electricpower supply controller 374 outputs a supply termination signal.

In step S24, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals that are input from the electric power supplycontrollers 374 of all of the devices to which electric power isre-supplied.

In step S25, the image capture permission instructing unit 384 outputs amessage representing permission to capture an image to the mobileterminal 42, based on the electric power supply completion signal inputfrom the electric power supply completion output unit 388. Thereafter,control returns to step S16 shown in FIG. 24 and steps subsequentthereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S18, then control proceeds to step S26, inwhich the image capture completion determiner 386 determines whether ornot the image capturing process is completed, by comparing the number oftimes that radiographic images have been captured in the image capturingconditions with the count from the counter 380. If the count is smallerthan the number of times that radiographic images have been captured,then control returns to step S16 shown in FIG. 24, and step S16 andsteps subsequent thereto are repeated until the image capturing processis brought to an end. If the image capturing process is completed,control proceeds to step S27, in which the electric power controller 334is temporarily shut down. More specifically, the image capturecompletion determiner 386 outputs an image capture completion signal.Based on the image capture completion signal input from the imagecapture completion determiner 386, the pause processor 340 outputs apause signal to the electric power controller 334. Based on the pausesignal input from the pause processor 340, the electric power controller334 stops controlling supply of electric power, and waits to beactivated at a subsequent time by the electric power supply activator336.

In step S28, the activator/deactivator 332 performs a determiningprocess. More specifically, if the activator/deactivator 332 is thefirst activator/deactivator 332A, then the first activator/deactivator332A determines whether or not the first present position is outside ofthe medical organization. If the first present position remains outsideof the medical organization, then control returns to step S4 shown inFIG. 23, and step S4 and steps subsequent thereto are repeated. If theoperator 38 carries the first radiographic image capturing apparatus10A, the devices of which are coupled together, into the medicalorganization while gripping the grip 24, then control proceeds to stepS29 shown in FIG. 24, in which the electric power supply activator 336is fully deactivated. More specifically, when the first radiographicimage capturing apparatus 10A is carried into the medical organization,the first activator/deactivator 332A outputs a full deactivation signal.Based on the full deactivation signal, the electric power supplyactivator 336 is shut down, and the electric power supply activator 336waits to be reactivated at a subsequent time by the firstactivator/deactivator 332A. At this stage, the operation sequence of thefirst radiographic image capturing apparatus 10A is brought to an end.However, when the first radiographic image capturing apparatus 10A iscarried out of the medical organization again, step S2 shown in FIG. 23and steps subsequent thereto are repeated.

If the activator/deactivator 332 is the second activator/deactivator332B, then in step S28, the second activator/deactivator 332B determineswhether or not the second present position remains within the presetlocation.

If the second present position remains in the preset location, thencontrol returns to step S4 shown in FIG. 23, and step S4 and stepssubsequent thereto are repeated. If the operator 38 carries the firstradiographic image capturing apparatus 10A, devices of which are coupledtogether, out of the preset location while gripping the grip 24, thencontrol proceeds to step S29 shown in FIG. 24, in which the electricpower supply activator 336 is fully deactivated. More specifically, whenthe first radiographic image capturing apparatus 10A is carried outsideof the preset location, the second activator/deactivator 332B outputs afull deactivation signal. Based on the full deactivation signal, theelectric power supply activator 336 is shut down, and the electric powersupply activator 336 waits to be activated at a subsequent time by thesecond activator/deactivator 332B. At this stage, the operation sequenceof the first radiographic image capturing apparatus 10A is brought to anend. However, when the first radiographic image capturing apparatus 10Ais carried again into the preset location, or is carried into a newpreset location, step S2 shown in FIG. 23 and steps subsequent theretoare repeated.

If the activator/deactivator 332 is the third activator/deactivator332C, then in step S28, the third activator/deactivator 332C determineswhether or not the distance between the aforesaid device and anotherdevice satisfies the certain condition. If the distance between theaforesaid device and another device still satisfies the certaincondition, then control returns to step S4 shown in FIG. 23, and step S4and steps subsequent thereto are repeated. If the operator 38 separatesthe radiation source device 18 and the cassette 12 of the firstradiographic image capturing apparatus 10A from each other, whereuponthe linear distance between the devices exceeds the reference distance,or the distance between the devices falls outside of the communicationrange, or if the distance between the devices is too large for thedevices to be connected in a wired or wireless fashion, then controlproceeds to step S29 shown in FIG. 24, in which the electric powersupply activator 336 is fully deactivated. The thirdactivator/deactivator 332C outputs a full deactivation signal. Based onthe full deactivation signal, the electric power supply activator 336 isshut down and waits to be activated at a subsequent time by the thirdactivator/deactivator 332C. At this stage, the operation sequence of thefirst radiographic image capturing apparatus 10A is brought to an end.However, when the distance between the aforesaid device and anotherdevice once again satisfies the certain condition, step S2 shown in FIG.23 and steps subsequent thereto are repeated.

An operation sequence of the first radiographic image capturingapparatus 10A, if the supply timing conditions indicate supply ofelectric power before capturing of radiographic images, will bedescribed below with reference to the flowcharts shown in FIGS. 25through 27. Although the electric power manager 390 mainly is involvedin the operation sequence to be described below, the cassette selector364 and the integrated supply 368 may also be included in the operationsequence.

In step S101 shown in FIG. 25, the activator/deactivator 332 performs adetermining process. More specifically, if the activator/deactivator 332is the first activator/deactivator 332A (see FIGS. 15A and 15B), thenthe first activator/deactivator 332A determines whether or not the firstpresent position is outside of a medical organization. If the operator38 carries the first radiographic image capturing apparatus 10A, thedevices of which are coupled together, out of the medical organizationwhile gripping the grip 24, then control proceeds to step S102, in whichthe first activator/deactivator 332A outputs an activation signal.

If the activator/deactivator 332 is the second activator/deactivator332B, then the second activator/deactivator 332B determines whether ornot the second present position is in a preset location, i.e., alocation indicated by area information registered in the second locationinformation table 331B. If the operator 38 carries the firstradiographic image capturing apparatus 10A, the devices of which arecoupled together, into the preset location while gripping the grip 24,then control proceeds to step S102, in which the secondactivator/deactivator 332B outputs an activation signal.

If the activator/deactivator 332 is the third activator/deactivator332C, then the third activator/deactivator 332C determines whether ornot the distance between the aforesaid device and another devicesatisfies a certain condition. This determining process is the same asthe determining process described above in step S1, and will not bedescribed below. When the operator 38 approaches the radiation sourcedevice 18 and the cassette 12 of the first radiographic image capturingapparatus 10A toward each other until the linear distance between thedevices is equal to or less than the reference distance, or when thedistance between the devices enters within a communication range, orwhen the distance between the devices allows them to be connected in awired or wireless fashion, the third activator/deactivator 332C outputsan activation signal in step S102.

Thereafter, in step S103, the electric power supply permissioninstructing unit 350 outputs a message to the mobile terminal 42 forprompting the operator 38 to enter image capturing conditions.

In step S104, the electric power supply activator 336 activates theelectric power controller 334 based on the present image capturingconditions (order) entered from the mobile terminal 42. At this time,only the electric power supply activator 336 of a device having an ID,which is the same as the ID of the radiation source device 18 or thecassette 12 used to capture radiation images, which has been registeredin advance in the image capturing conditions, activates thecorresponding electric power controller 334. The present image capturingconditions may be input from the data center via the network and themobile terminal 42. The present image capturing conditions are stored inthe memory 330.

In step S105, the device connection detector 360 detects whether or notthe device, i.e., the radiation source device 18 or the cassette 12, isconnected to the first energy input/output unit 300 or the second energyinput/output unit 302. If the activator/deactivator 332 is the thirdactivator/deactivator 332C (see FIG. 17C) according to the third mode,then since the device connection detector 360 has already detected theconnection in step S101, control proceeds from step S104 to step S106,while skipping step S105.

After the device connection detector 360 has detected the connection instep S105, control proceeds to step S106, in which the ID acquirer 410of the electric power manager 390 shown in FIG. 22 acquires the ID ofthe connected device. More specifically, the ID acquirer 410 sends atransfer request requesting the connected device to transfer the IDthereof. The connected device outputs the ID to the electric powermanager 390, and the ID acquirer 410 acquires the ID and stores the IDin the memory 330.

In step S107, the information acquirer 412 for acquiring variousinformation acquires the present image capturing conditions, whichalready have been stored in the memory 330, a remaininglevel-of-electric-energy information table corresponding to the ID,previous image capturing conditions corresponding to the ID, and a usagehistory table corresponding to the ID, and stores such information inthe memory 330.

In step S108, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the radiationsource device 18 and the cassette 12 that is used to captureradiographic images, from conditions concerning the amount of electricpower to be supplied (stored in the memory 330), and the present orprevious image capturing conditions, which represent the number ofradiographic images to be captured, mAs values, etc., from among thebattery charging conditions. The amount-of-consumed-electric-powerpredictor 414 then corrects the calculated amounts of electric power bymultiplying the calculated amounts by usage histories of the radiationsource device 18 and the cassette 12, i.e., by coefficientscorresponding to the number of times that the radiation source device 18and the cassette 12 have been used, thereby predicting amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 during the present image capturing process, or amountsof electric power consumed by the radiation source device 18 and thecassette 12 during the previous image capturing process. The conditionconcerning amount of electric power from among the battery chargingconditions may be an amount of electric power required to captureradiographic images in the present image capturing process, an amount ofelectric power required to capture a single radiographic image, or anamount of electric power consumed during the previous image capturingprocess. If the condition concerning the amount of electric power is anamount of electric power required to capture radiographic images duringthe present image capturing process, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 used to capture radiographic images in the present imagecapturing process, and corrects the calculated amounts of electric powerby multiplying the calculated amounts by usage histories of theradiation source device 18 and the cassette 12, i.e., by coefficientscorresponding to the number of times that the radiation source device 18and the cassette 12 have been used, thereby predicting amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 during the present image capturing process, or amountsof electric power consumed by the radiation source device 18 and thecassette 12 during the previous image capturing process. If thecondition concerning amount of electric power is an amount of electricpower consumed during the previous image capturing process, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power consumed by the radiation source device 18 and thecassette 12 in the previous image capturing process, and corrects thecalculated amounts of electric power by multiplying the calculatedamounts by usage histories of the radiation source device 18 and thecassette 12, i.e., by coefficients corresponding to the number of timesthat the radiation source device 18 and the cassette 12 have been used,thereby predicting amounts of electric power consumed by the radiationsource device 18 and the cassette 12 during the previous image capturingprocess.

In step S109, the electric power supply route setting unit 370 sets aroute for supply of electric power based on the predicted amounts ofelectric power, and the remaining levels of electric power in thebatteries 308 of the radiation source device 18 and the cassette 12(remaining level-of-electric-energy information tables). Typically, theelectric power supply route setting unit 370 sets a route for supply ofelectric power to a device, the battery of which stores a remaininglevel of electric power that will be almost eliminated during thepresent image capturing process. Information concerning the set route isdisplayed on the display screen of the mobile terminal 42. If theoperator 38 intends to supply electric power additionally from otherdevices, i.e., a radiation source device 18 and a cassette 12 that arenot used to capture radiographic images, then the operator 38 entersroutes for supplying electric power from such other devices, i.e.,routes for supplying electric power from the other devices to thedevices having IDs, together with amounts of electric power. If theoperator 38 intends to charge a battery as well using another device,i.e., a radiation source device 18 or a cassette 12, then the operator38 enters a route for supplying electric power to or from the otherdevice, i.e., a route from the other device to the radiation sourcedevice 18 or the cassette 12 that is used to capture radiographicimages, or a route from the radiation source device 18 or the cassette12 that is used to capture radiographic images to the other device,together with an amount of electric power to be supplied and the orderin which electric power is supplied. Based on the entered route forsupplying electric power, the electric power supply route setting unit370 outputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachof such devices.

In step S110, the amount-of-supplied-electric-power setting unit 372sets an amount of electric power to be supplied (supplied amount ofelectric power) based on the predicted amount of electric power and theremaining levels of electric power in the batteries 308 of the radiationsource device 18 and the cassette 12 (remaining level-of-electric-energyinformation tables). Thus, at most, the predicted amount of electricpower is supplied to a device, the battery of which stores a remaininglevel of electric power that will be almost eliminated during thepresent image capturing process. The amount of electric power, which issupplied to such a device, may be one-half or one-third the predictedamount of electric power. The information of the set amount of electricpower is displayed on a display screen of the mobile terminal 42. Theset amount of electric power also can be changed as desired by themobile terminal 42. If the operator 38 intends to charge a battery aswell, then the amount-of-supplied-electric-power setting unit 372 alsosets an amount of electric power to be supplied additionally to chargethe battery. The amount of electric power, which is predicted based onthe previous image capturing conditions, is supplied in order tosupplement the amount of electric power consumed during the previousimage capturing process. If the operator 38 intends to charge a batteryas well, then the amount-of-supplied-electric-power setting unit 372also sets an amount of electric power to be supplied additionally tocharge the battery. The set amount of electric power is supplied to theelectric power supply controller 374 of the corresponding device.

In step S111, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power. If theelectric power supply controller 374 is supplied with a supplydestination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308 orsupply of electric power from the battery 308 is completed, the electricpower supply controller 374 outputs a supply termination signal.

In step S112, the information updater 416 of the electric power manager390, in the remaining level-of-electric-energy information table,subtracts the amount of supplied electric power from the remaining levelof electric power of the device that serves as the electric power supplysource, and adds the amount of supplied electric power to the remaininglevel of electric power of the device that serves as the electric powersupply destination.

In step S113, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been supplied.

In step S114, the image capture permission instructing unit 384 outputsa message, which represents permission to capture an image, to themobile terminal 42 based on the electric power supply completion signalinput from the electric power supply completion output unit 388.

In step S115 shown in FIG. 26, the operator 38 prepares the firstradiographic image capturing apparatus 10A for capturing radiographicimages, at a site to which the first radiographic image capturingapparatus 10A has been carried. This preparatory procedure has alreadybeen described in detail above, and will not be described below.

In step S116, the operator 38 turns on the exposure switch 48 in orderto start capturing radiographic images of the subject 50. At this time,the counter 380 updates the count thereof by incrementing the count by+1.

When the operator 38 turns on the exposure switch 48 in step S116, theelectric power supply limiter 338 outputs a supply limit signal to theelectric power controller 334, during the period referred to above instep S117. During the period in which the electric power controller 334is supplied with the supply limit signal, the electric power supplyoperation of the electric power controller 334 is limited.

In step S118, the remaining level prediction updater 392 updates, by wayof subtraction, the remaining levels of electric power stored in thebatteries, which are recorded in the remaining level-of-electric-energyinformation tables, i.e., the remaining levels of electric power storedin the batteries 308 of the radiation source device 18 and the cassette12, which are utilized for capturing radiographic images. Morespecifically, with respect to the radiation source device 18 and thecassette 12 that carry out capturing of radiographic images, theremaining level prediction updater 392 calculates the amounts ofelectric power consumed during each time the exposure switch 48 isturned on, based on the image capturing conditions and the usage historytables, and subtracts the calculated amounts of electric power from theremaining levels of electric power stored in the batteries 308 of theradiation source device 18 and the cassette 12, which are recorded inthe remaining level-of-electric-energy information tables.

In step S119, the electric power controller 334 determines whether ornot electric power needs to be re-supplied, based on whether theelectric power supply controller 374 of any device has output an imagingdisabled signal.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S120, in which the imagecapture interruption instructing unit 378 outputs a message indicativeof an image capture interruption to the mobile terminal 42. The mobileterminal 42 displays the message on a display screen thereof, andpreferably outputs an alarm sound, for prompting the operator 38 tointerrupt the image capturing process.

Thereafter, in step S121, the re-supply instructing unit 382 outputs are-supply instruction signal to the electric power supply route settingunit 370, the amount-of-supplied-electric-power setting unit 372, andthe electric power manager 390.

In step S122, the electric power supply route setting unit 370 sets, asa re-supply route, a route for supplying electric power to the devicehaving the ID included in the input re-supply instruction signal, andoutputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachdevice, based on the set re-supply route.

In step S123, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the device havingthe aforementioned ID, i.e., the radiation source device 18 or thecassette 12 that is re-supplied with electric power, from among theimage capturing conditions for an image capturing process to be carriedout, and from which image capturing conditions for radiographic imagesalready captured (indicated by the count) are excluded, among thebattery charging conditions stored in the memory 330 and the presentimage capturing conditions representative of the number of radiographicimages to be captured, mAs values, etc. Theamount-of-consumed-electric-power predictor 414 also corrects thecalculated amounts of electric power by multiplying the calculatedamounts by the usage history of the device having the ID, i.e., acoefficient corresponding to the number of times that the device of theID has been used, thereby predicting an amount of electric power thatwill be consumed by the device of the ID in the image capturing processto be carried out.

In step S124, the amount-of-supplied-electric-power setting unit 372sets the amount of electric power predicted by theamount-of-consumed-electric-power predictor 414, as an amount ofre-supplied electric power, and supplies information concerning the setamount of re-supplied electric power to the electric power supplycontroller 374 of the corresponding device.

In step S125, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power. If theelectric power supply controller 374 is supplied with a supplydestination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308 orsupply of electric power from the battery 308 is completed, the electricpower supply controller 374 outputs a supply termination signal.

In step S126, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been re-supplied.

In step S127, the image capture permission instructing unit 384 outputsa message to the mobile terminal 42 representing permission to captureimages, based on the electric power supply completion signal input fromthe electric power supply completion output unit 388. Thereafter,control returns to step S116 and steps subsequent thereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S119, then control proceeds to step S128 shownin FIG. 27, in which the image capture completion determiner 386determines whether or not the image capturing process is completed bycomparing the number of times that radiographic images have beencaptured in the image capturing conditions with the count of the counter380. If the count is smaller than the number of times that radiographicimages have been captured, then control returns to step S116 shown inFIG. 26, and step S116 and steps subsequent thereto are repeated untilthe image capturing process is brought to an end. If the image capturingprocess is completed, control proceeds to step S129 shown in FIG. 27, inwhich the usage history updater 394 adds the number of times that theexposure switch 48 has been turned on to the number of times recorded inthe usage history table, i.e., the number of times that the radiationsource device 18 and the cassette 12 have been used to captureradiographic images.

In step S130, the remaining level information transfer unit 396transfers the remaining level information table via the network to thedatabase of the data center for updating.

In step S131, the usage history transfer unit 398 transfers the usagehistory table via the network to the database of the data center forupdating.

In step S132, the electric power controller 334 is temporarily shutdown. More specifically, the image capture completion determiner 386outputs an image capture completion signal. Based on the image capturecompletion signal input from the image capture completion determiner386, the pause processor 340 outputs a pause signal to the electricpower controller 334. Based on the pause signal input from the pauseprocessor 340, the electric power controller 334 stops controllingsupply of electric power, and waits to be activated at a subsequent timeby the electric power supply activator 336.

In step S133, the activator/deactivator 332 performs a determiningprocess. More specifically, if the activator/deactivator 332 is thefirst activator/deactivator 332A, then the first activator/deactivator332A determines whether or not the first present position is outside ofthe medical organization. If the first present position remains outsideof the medical organization, then control returns to step S104 shown inFIG. 25, and step S104 and steps subsequent thereto are repeated. If theoperator 38 carries the first radiographic image capturing apparatus10A, the devices of which are coupled together, into the medicalorganization while gripping the grip 24, then control proceeds to stepS134 shown in FIG. 27, in which the electric power supply activator 336is fully deactivated. More specifically, when the first radiographicimage capturing apparatus 10A is carried into the medical organization,the first activator/deactivator 332A outputs a full deactivation signal.Based on the full deactivation signal, the electric power supplyactivator 336 is shut down and waits to be activated at a subsequenttime by the first activator/deactivator 332A. At this stage, theoperation sequence of the first radiographic image capturing apparatus10A is brought to an end. However, when the first radiographic imagecapturing apparatus 10A is carried outside of the medical organizationagain, then step S102 shown in FIG. 25 and steps subsequent thereto arerepeated.

If the activator/deactivator 332 is the second activator/deactivator332B, then in step S133, the second activator/deactivator 332Bdetermines whether or not the second present position is in the presetlocation. If the second present position remains in the preset location,then control returns step S104 shown in FIG. 25, and step S104 and stepssubsequent thereto are repeated. If the operator 38 carries the firstradiographic image capturing apparatus 10A, the devices of which arecoupled together, outside of the preset location while gripping the grip24, then control proceeds to step S134 shown in FIG. 27, in which theelectric power supply activator 336 is fully deactivated. Morespecifically, when the first radiographic image capturing apparatus 10Ais carried outside of the preset location, the secondactivator/deactivator 332B outputs a full deactivation signal. Based onthe full deactivation signal, the electric power supply activator 336 isshut down and waits to be activated at a subsequent time by the secondactivator/deactivator 332B. At this stage, the operation sequence of thefirst radiographic image capturing apparatus 10A is brought to an end.However, when the first radiographic image capturing apparatus 10A iscarried into the preset location again, or into a new preset location,step S102 shown in FIG. 25 and steps subsequent thereto are repeated.

If the activator/deactivator 332 is the third activator/deactivator332C, then in step S133, the third activator/deactivator 332C determineswhether or not the distance between the aforesaid device and anotherdevice satisfies the certain condition. If the distance between theaforesaid device and another device still satisfies the certaincondition, then control returns to step S104 shown in FIG. 25, and stepS104 and steps subsequent thereto are repeated. If the operator 38separates the radiation source device 18 and the cassette 12 of thefirst radiographic image capturing apparatus 10A from each other,whereby the linear distance between the devices exceeds the referencedistance, if the distance between the devices falls outside of thecommunication range, or if the distance between the devices is too largefor the devices to be connected in a wired or wireless fashion, thencontrol proceeds to step S134 shown in FIG. 27, in which the electricpower supply activator 336 is fully deactivated. More specifically, thethird activator/deactivator 332C outputs a full deactivation signal.Based on the full deactivation signal, the electric power supplyactivator 336 is shut down and waits to be activated at a subsequenttime by the third activator/deactivator 332C. At this stage, theoperation sequence of the first radiographic image capturing apparatus10A is brought to an end. However, when the distance between theaforesaid device and another device again satisfies the certaincondition, step S102 shown in FIG. 25 and steps subsequent thereto arerepeated.

An operation sequence of the first radiographic image capturingapparatus 10A, if the supply timing conditions indicate supply ofelectric power after capturing of radiographic images, will be describedbelow with reference to the flowcharts shown in FIGS. 28 and 29.Although the electric power manager 390 mainly is involved in theoperation sequence to be described below, the cassette selector 364 andthe integrated supply 368 may also be included in the operationsequence.

In step S201 shown in FIG. 28, the activator/deactivator 332 performs adetermining process. More specifically, if the activator/deactivator 332is the first activator/deactivator 332A, then the firstactivator/deactivator 332A determines whether or not the first presentposition is outside of a medical organization. If the operator 38carries the first radiographic image capturing apparatus 10A, thedevices of which are coupled together, outside of the medicalorganization while gripping the grip 24, then control proceeds to stepS202, in which the first activator/deactivator 332A outputs anactivation signal.

If the activator/deactivator 332 is the second activator/deactivator332B, then the second activator/deactivator 332B determines whether ornot the second present position is in a preset location, i.e., at alocation indicated by area information registered in the second locationinformation table 331B. If the operator 38 carries the firstradiographic image capturing apparatus 10A, the devices of which arecoupled together, into the preset location while gripping the grip 24,then control proceeds to step S202, in which the secondactivator/deactivator 332B outputs an activation signal.

If the activator/deactivator 332 is the third activator/deactivator332C, then the third activator/deactivator 332C determines whether ornot the distance between the aforesaid device and another devicesatisfies a certain condition. The determining process is the same asthe determining process described above in step S1, and will not bedescribed below. When the operator 38 approaches the radiation sourcedevice 18 and the cassette 12 of the first radiographic image capturingapparatus 10A toward each other until the linear distance between thedevices is equal to or smaller than the reference distance, when thedistance between the devices enters within the communication range, orwhen the distance between the devices allows them to be connected in awired or wireless fashion, the third activator/deactivator 332C outputsan activation signal in step S202.

Thereafter, in step S203, the electric power supply permissioninstructing unit 350 outputs a message for prompting the operator 38 toenter image capturing conditions to the mobile terminal 42.

In step S204, the operator 38 prepares the first radiographic imagecapturing apparatus 10A for capturing radiographic images at a sitewhere the first radiographic image capturing apparatus 10A has beencarried. In step S205, the operator 38 turns on the exposure switch 48to start capturing radiographic images of the subject 50.

In step S206, the electric power controller 334 determines whether ornot electric power needs to be re-supplied, based on whether theelectric power supply controller 374 of any given device has output animaging disabled signal.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S207, in which the imagecapture interruption instructing unit 378 outputs a message indicatinginterruption of image capturing to the mobile terminal 42. Thereafter,in step S208, the re-supply instructing unit 382 outputs a re-supplyinstruction signal to the electric power supply route setting unit 370,the amount-of-supplied-electric-power setting unit 372, and the electricpower manager 390, thereby activating the electric power supply routesetting unit 370, the amount-of-supplied-electric-power setting unit372, and the electric power manager 390 in an interrupt routine.

In step S209, the electric power supply route setting unit 370 sets aroute for supplying electric power to the device having the ID includedin the input re-supply instruction signal, as a re-supply route, andbased on the set re-supply route, outputs a supply source instructionsignal or a supply destination instruction signal to the electric powersupply controller 374 of each device.

In step S210, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power that are consumed by the devicehaving the ID, i.e., the radiation source device 18 or the cassette 12that are re-supplied with electric power, from image capturingconditions for an image capturing process to be carried out, from whichimage capturing conditions for radiographic images already captured(indicated by the count) are excluded, from among the battery chargingconditions stored in the memory 330, and the present image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc. The amount-of-consumed-electric-powerpredictor 414 also corrects the calculated amounts of electric power bymultiplying the calculated amounts by a usage history of the device ofthe ID, i.e., a coefficient corresponding to the number of times thatthe device of the ID has been used, thereby predicting an amount ofelectric power to be consumed by the device of the ID in the imagecapturing process to be carried out.

In step S211, the amount-of-supplied-electric-power setting unit 372sets the amount of electric power predicted by theamount-of-consumed-electric-power predictor 414 as an amount ofre-supplied electric power, and outputs the information concerning theset amount of re-supplied electric power to the electric power supplycontroller 374 of the corresponding device.

In step S212, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power.Further, if the electric power supply controller 374 is supplied with asupply destination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308 orsupply of electric power from the battery 308 is completed, then theelectric power supply controller 374 outputs a supply terminationsignal.

In step S213, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals, which are input from the electric power supplycontrollers 374 of all of the devices to which electric power has beenre-supplied.

In step S214, the image capture permission instructing unit 384 outputsa message representing permission to capture an image to the mobileterminal 42, based on the electric power supply completion signal inputfrom the electric power supply completion output unit 388. Thereafter,control returns to step S205 and steps subsequent thereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S206, then control proceeds to step S215, inwhich the image capture completion determiner 386 determines whether ornot the image capturing process is completed. If the image capturingprocess is not completed, then control returns to step S205, and stepS205 and steps subsequent thereto are repeated until the image capturingprocess is brought to an end. If the image capturing process hasfinished, control proceeds to step S216, in which the electric powersupply activator 336 activates the electric power controller 334 basedon an image capture completion signal input from the image capturecompletion determiner 386. At this time, only the electric power supplyactivator 336 of a device having an ID that is the same as the ID of theradiation source device 18 or the cassette 12 that is used to captureradiation images, which has been registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334.

In step S217 shown in FIG. 29, the device connection detector 360detects whether or not the device is connected to the first energyinput/output unit 300 or the second energy input/output unit 302. If theactivator/deactivator 332 is the third activator/deactivator 332C (seeFIG. 17C) according to the third mode, then since the device connectiondetector 360 has already detected the connection in step S201, controlproceeds from step S216 to step S218, while skipping step S217.

After the device connection detector 360 has detected the connection instep S217, control proceeds to step S218, in which the ID acquirer 410of the electric power manager 390 acquires the ID of the connecteddevice. Thereafter, in step S219, the information acquirer 412 foracquiring various information acquires the present image capturingconditions, which have already been stored in the memory 330, aremaining level-of-electric-energy information table corresponding tothe ID, previous image capturing conditions corresponding to the ID, anda usage history table corresponding to the ID, and stores suchinformation in the memory 330.

In step S220, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the radiationsource device 18 and the cassette 12, which are used to captureradiographic images, from a condition concerning the amount of electricpower to be supplied, and the present or previous image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc., from among the battery charging conditions.

In step S221, the electric power supply route setting unit 370 sets aroute for supply of electric power, based on the predicted amounts ofelectric power and the remaining levels of electric power in thebatteries 308 of the radiation source device 18 and the cassette 12(remaining level-of-electric-energy information tables).

Thereafter, in step S222, the amount-of-supplied-electric-power settingunit 372 sets an amount of electric power to be supplied (suppliedamount of electric power), based on the predicted amount of electricpower, and the remaining levels of electric power in the batteries 308of the radiation source device 18 and the cassette 12 (remaininglevel-of-electric-energy information tables).

In step S223, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power.Further, if the electric power supply controller 374 is supplied with asupply destination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. When supply of electric power to the battery 308 orsupply of electric power from the battery 308 is completed, the electricpower supply controller 374 outputs a supply termination signal.

In step S224, the information updater 416, in the remaininglevel-of-electric-energy information table, subtracts the amount ofsupplied electric power from the remaining level of electric power ofthe device that serves as an electric power supply source, and adds theamount of supplied electric power to the remaining level of electricpower of the device that serves as an electric power supply destination.

In step S225, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been supplied.

In step S226, the usage history updater 394 adds the number of timesthat the exposure switch 48 has been turned on to the number of timesrecorded in the usage history table, i.e., the number of times that theradiation source device 18 and the cassette 12 have been used to captureradiographic images.

In step S227, the remaining level information transfer unit 396transfers the remaining level information table via the network to thedatabase of the data center for updating. In step S228, the usagehistory transfer unit 398 transfers the usage history table via thenetwork to the database of the data center for updating. Thereafter, instep S229, the pause processor 340 temporarily shuts down the electricpower controller 334.

In step S230, the activator/deactivator 332 performs a determiningprocess. More specifically, if the activator/deactivator 332 is thefirst activator/deactivator 332A, then the first activator/deactivator332A determines whether or not the first present position lies outsideof the medical organization. If the first present position remainsoutside of the medical organization, then control returns to step S203shown in FIG. 28, and step S203 and steps subsequent thereto arerepeated. If the operator 38 carries the first radiographic imagecapturing apparatus 10A, the devices of which are coupled together, intothe medical organization while gripping the grip 24, then controlproceeds to step S231 shown in FIG. 29, in which the electric powersupply activator 336 is fully deactivated. More specifically, when thefirst radiographic image capturing apparatus 10A is carried into themedical organization, the first activator/deactivator 332A outputs afull deactivation signal. Based on the full deactivation signal, theelectric power supply activator 336 is shut down and waits to beactivated at a subsequent time by the first activator/deactivator 332A.At this stage, the operation sequence of the first radiographic imagecapturing apparatus 10A is brought to an end. However, when the firstradiographic image capturing apparatus 10A again is carried outside ofthe medical organization, step S202 shown in FIG. 28 and stepssubsequent thereto are repeated.

If the activator/deactivator 332 is the second activator/deactivator332B, then the second activator/deactivator 332B determines whether ornot the second present position is in the preset location in step S230.If the second present position remains in the preset location, thencontrol returns to step S203 shown in FIG. 28, and step S203 and stepssubsequent thereto are repeated. If the operator 38 carries the firstradiographic image capturing apparatus 10A, the devices of which arecoupled together, outside of the preset location while gripping the grip24, then control proceeds to step S231 shown in FIG. 29, in which theelectric power supply activator 336 is fully deactivated. Morespecifically, when the first radiographic image capturing apparatus 10Ais carried outside of the preset location, the secondactivator/deactivator 332B outputs a full deactivation signal. Based onthe full deactivation signal, the electric power supply activator 336 isshut down and waits to be activated at a subsequent time by the secondactivator/deactivator 332B. At this stage, the operation sequence of thefirst radiographic image capturing apparatus 10A is brought to an end.However, when the first radiographic image capturing apparatus 10A iscarried again into the preset location or into a new preset location,step S202 shown in FIG. 28 and steps subsequent thereto are repeated.

If the activator/deactivator 332 is the third activator/deactivator332C, then in step S230, the third activator/deactivator 332C determineswhether or not the distance between the aforesaid device and anotherdevice satisfies the certain condition. If the distance between theaforesaid device and another device still satisfies the certaincondition, then control returns to step S203 shown in FIG. 28, and stepS203 and steps subsequent thereto are repeated. If the operator 38separates the radiation source device 18 and the cassette 12 of thefirst radiographic image capturing apparatus 10A from each other, andthe linear distance between the devices exceeds the reference distance,if the distance between the devices falls outside of the communicationrange, or if the distance between the devices is too large for thedevices to be connected in a wired or wireless fashion, then controlproceeds to step S231 shown in FIG. 29, in which the electric powersupply activator 336 is fully deactivated. The thirdactivator/deactivator 332C outputs a full deactivation signal. Based onthe full deactivation signal, the electric power supply activator 336 isshut down, and the electric power supply activator 336 waits to beactivated at a subsequent time by the third activator/deactivator 332C.At this stage, the operation sequence of the first radiographic imagecapturing apparatus 10A is brought to an end. However, when the distancebetween the aforesaid device and another device again satisfies thecertain condition, step S202 shown in FIG. 28 and steps subsequentthereto are repeated.

Since the first radiographic image capturing apparatus 10A, whichincludes the first activator/deactivator 332A, is prevented from beingsupplied with electric power within a medical organization, the firstradiographic image capturing apparatus 10A can reduce consumption ofelectric power.

Furthermore, since the first radiographic image capturing apparatus 10A,which includes the second activator/deactivator 332B, is prevented frombeing supplied with electric power in places other than the presetlocation, the first radiographic image capturing apparatus 10A canreduce consumption of electric power.

If a home-care service site is registered as the preset location, thenthe first radiographic image capturing apparatus 10A can easily captureradiographic images of examinees at their homes.

When needs arise for capturing radiographic images at accident sites,disaster sites, or medical organizations such as clinics that do nothave radiation facilities, the first radiographic image capturingapparatus 10A can be carried to such a site, and the site can quickly beregistered as a preset location using GPS or the like. Once the site hasbeen registered as the preset location, the first radiographic imagecapturing apparatus 10A can quickly start capturing radiographic imagesof an examinee, such as an accident victim, a disaster victim, or apatient, without requiring the examinee to be moved to a mobile medicalcheckup motor vehicle or an image capturing chamber.

The first radiographic image capturing apparatus 10A, which includes thesecond activator/deactivator 332B, is capable of presetting a locationby way of absolute positioning, and also of presetting a location by wayof relative positioning. Presetting a location by way of relativepositioning offers the following advantages. While the operator of thefirst radiographic image capturing apparatus 10A is on board a transportvehicle, the operator designates the transport vehicle as a presetlocation. Then, the present position of the transport vehicle isregistered as area information, which is representative a relativeposition, in a location information table. Inasmuch as the areainformation varies periodically as the transport vehicle moves, thepresent position and the area information, which is representative ofthe relative position, can be compared with each other in the samemanner as the present position and the area information, which isrepresentative of the absolute position, are compared with each other,as described above. Since fixed locations such as buildings, land, etc.,and also moving objects (locations) such as transport vehicles includingambulances, mobile medical checkup motor vehicles, railway cars, ships,aircrafts, etc., can be registered as preset locations, it is possiblefor the first radiographic image capturing apparatus 10A to quicklystart capturing radiographic images of an examinee, such as an accidentvictim, a disaster victim, or a patient in a transport vehicle, withoutrequiring the examinee to be moved to a hospital having a radiationfacility.

Since the first radiographic image capturing apparatus 10A, whichincludes the third activator/deactivator 332C, is prevented from beingsupplied with electric power until the distance between the cassette 12and the radiation source device 18 of the first radiographic imagecapturing apparatus 10A satisfies a certain condition, the firstradiographic image capturing apparatus 10A can reduce consumption ofelectric power.

As soon as the distance between the cassette 12 and the radiation sourcedevice 18 satisfies the certain condition, the first radiographic imagecapturing apparatus 10A is made capable of capturing radiographic imagesof examinees. Consequently, the first radiographic image capturingapparatus 10A is convenient to use.

If the cassette 12 and the radiation source device 18 are separatelystored and carried, then the cassette 12 and the radiation source device18 are protected against being stolen as a set.

The first radiographic image capturing apparatus 10A, which incorporatestherein any one of the first activator/deactivator 332A, the secondactivator/deactivator 332B, and the third activator/deactivator 332C,offers the following common advantages:

(1) The first radiographic image capturing apparatus 10A requires onlythe batteries 308 of the radiation source device 18 and the cassette 12as power supplies thereof. Therefore, the first radiographic imagecapturing apparatus 10A is small in size and weight when carried, and isconvenient to use (e.g., is portable).

(2) If the electric power controller 334 controls electric powersupplied only along a route from the radiation source device 18 to thecassette 12, then a built-in capacitor may be used as the battery 308 ofthe cassette 12. In such a case, since a separate battery is notrequired as the battery 308 for the cassette 12, the user is able tocarry the first radiographic image capturing apparatus 10A easily.

(3) Similarly, if the electric power controller 334 controls electricpower so as to be supplied with power only along a route from thecassette 12 to the radiation source device 18, then a built-in capacitormay be used as the battery 308 of the radiation source device 18. Insuch a case, since a separate battery is not required as the battery 308for the radiation source device 18, the user is able to carry the firstradiographic image capturing apparatus 10A easily.

(4) When an unexpected need arises to capture radiographic images, e.g.,when it is necessary to recapture radiographic images, or if anadditional order comes up to capture radiographic images, whileradiographic images are being captured on a medical checkup vehicle, thefirst radiographic image capturing apparatus 10A can meet such a need.Instead of the medical checkup vehicle, the first radiographic imagecapturing apparatus 10A itself may be used.

(5) For capturing radiographic images in a region where a home powersupply is provided by a new form of energy, the first radiographic imagecapturing apparatus 10A can be used in order to minimize consumption ofelectric power generated from such a new form of energy.

(6) When a need arises to capture radiographic images of examinees ataccident sites, disaster sites, or on transport vehicles such asambulances (while in movement or at rest), railway cars, ships,aircrafts, or the like, the first radiographic image capturing apparatus10A can be used quickly to start capturing radiographic images of anexaminee, such as an accident victim or a disaster victim, withoutrequiring the examinee to be moved unduly to a mobile medical checkupmotor vehicle. While on a transport vehicle, the first radiographicimage capturing apparatus 10A can quickly begin capturing radiographicimages of the examinee, without having to wait for the transport vehicleto arrive at a station, a port, or an airport. While on an ambulance,the first radiographic image capturing apparatus 10A can send capturedradiographic image information to a medical organization such as ahospital before the ambulance reaches the hospital. As a consequence, adoctor at the hospital can recognize the condition of the examinee inadvance, and hence can quickly prepare the examinee for treatment.

(7) It is possible to carry several first radiographic image capturingapparatus 10A on a mobile medical checkup motor vehicle to performperiodic or temporary medical checkups at schools or large corporationswhere the number of examinees is large. Usually, since a single mobilemedical checkup motor vehicle, which is equipped with a single ordinaryradiographic image capturing apparatus, is dispatched to such locations,it has been customary for such examinees to have to wait a very longtime before radiographic images of the examinees can be captured.According to the present invention, several first radiographic imagecapturing apparatus 10A can be used simultaneously in order to minimizethe waiting time before radiographic images of examinees can becaptured.

(8) Electric power can be supplied along a wired route or a wirelessroute. For example, electric power can be supplied along a route from aradiation source device 18 used in an image capturing process to acassette 12 used in the image capturing process, along a route fromanother radiation source device 18, which is not used in an imagecapturing process, to the cassette 12 that is used in the imagecapturing process, or along a route from another cassette 12, which isnot used in an image capturing process, to the cassette 12 that is usedin the image capturing process.

(9) In addition, electric power can be supplied along a route from acassette 12 used in an image capturing process to a radiation sourcedevice 18 used in the image capturing process, or along a route fromanother radiation source device 18, which is not used in an imagecapturing process, to the radiation source device 18 that is used in theimage capturing process. Electric power can be supplied to a device,e.g., the radiation source device 18 or the cassette 12, in a wirelessfashion, when the device enters into an area enabling wireless feedingof power thereto.

(10) If an electric power supply route is fixed to a route from theradiation source device 18 to the cassette 12, or from the cassette 12to the radiation source device 18, then since a user is required toconfirm only the level of electric power in the supply source, apreparatory process for supplying electric power can be simplified, andradiographic images can be captured quickly.

(11) If the first energy input/output unit 300 is used via a wiredconnection and the second energy input/output unit 302 is used via awireless connection, then composite connections are made available forsupplying electric power. For example, electric power can be suppliedalong a route from the radiation source device 18 to the cassette 12 andanother radiation source device 18, along a route from the radiationsource device 18 to the cassette 12 and another cassette 12, along aroute from the cassette 12 to the radiation source device 18 and anothercassette 12, or along a route from the cassette 12 to the radiationsource device 18 and another radiation source device 18.

(12) The radiation source device 18 is supplied with electric powerpreferentially from a cassette 12 that has been deteriorated greatly, orfrom a cassette 12 having a small remaining built-in memory capacity.Therefore, electric power stored in a cassette 12, which has not beendeteriorated greatly, or in a cassette 12 having a large remainingbuilt-in memory capacity, can be saved, thereby enabling the firstradiographic image capturing apparatus 10A to be readily available foremergencies.

(13) The radiation source device 18 is supplied with electric powerpreferentially from a cassette 12 that is located closer to theradiation source device 18. Therefore, the time required to supplyelectric power to the radiation source device 18 is shortened, therebymaking the first radiographic image capturing apparatus 10A readilyavailable for emergencies.

(14) The radiation source device 18 is supplied with electric powerpreferentially from a cassette 12 that is smaller in size. Therefore,electric power stored in a cassette 12, which is larger in size andhence more versatile, can be saved, thereby making the firstradiographic image capturing apparatus 10A readily available foremergencies.

(15) Since the first radiographic image capturing apparatus 10A includesthe electric power manager 390, the level of electric power required tocapture a desired number of radiographic images is managed, so as tosupply electric power from a device, the battery of which storesexcessive electric power to a device having a battery with insufficientelectric power, for example, up to the level of the required electricpower. Therefore, the radiation source device 18 and the cassette 12 canbe supplied efficiently with electric power, thereby making the firstradiographic image capturing apparatus 10A readily available in anemergency. Further, since electric power required to captureradiographic images can flexibly be supplied from another device, whichis not used in the image capturing process, the first radiographic imagecapturing apparatus 10A can be made readily available for emergencies.

(16) The timing at which electric power is supplied can be determined asdesired. For example, the timing at which electric power is supplied canbe determined in order to supply electric energy before an imagecapturing process is carried out. In this manner, electric powerrequired to capture radiographic images can be ensured without wastefulelectric power consumption. Since electric power required to captureradiographic images is predicted and supplied in accordance therewith,electric power is supplied efficiently. If the timing at which electricpower is supplied is determined in order to supply electric energy afteran image capturing process has been performed, then since the amount ofelectric power required to capture at least one radiographic image isensured, the first radiographic image capturing apparatus 10A canquickly be readied to perform a next image capturing process.

(17) Supply of electric power is stopped during a period in which noiseis likely to be added to radiographic image information being captured.Consequently, wasteful consumption of electric power is minimized forenabling low electric power consumption, while at the same time thequality of the radiographic image information is prevented from becomingdegraded.

In the above embodiment, the battery controller 306 is provided in eachof the devices, e.g., the radiation source device 18 and the cassette12. However, among the components that make up the battery controller306, the electric power supply controller 374 and the remaining leveldetector 376 may be provided in each of the devices, whereas the othercomponents thereof may be provided only in the radiation source device18 or in the cassette 12 that is used in an image capturing process,e.g., in any one of a radiation source device 18, a cassette 12, and aPC 280, which are used in an image capturing process of a thirdradiographic image capturing apparatus 10C, to be described later. Amongthe components of the electric power controller 334, only the electricpower manager 390 may be provided in either one of the radiation sourcedevice 18 or the cassette 12 that is used in an image capturing process,e.g., in any one of the radiation source device 18, the cassette 12, andthe PC 280, which are used in an image capturing process of the thirdradiographic image capturing apparatus 10C, to be described later.

While the first radiographic image capturing apparatus 10A istransported, the radiation source device 18 and the cassette 12 arecoupled integrally to each other by the joining mechanism 82. While thefirst radiographic image capturing apparatus 10A operates to captureradiographic images, the radiation source device 18 and the cassette 12are separated from each other, and then the radiation source 44 of theradiation source device 18 emits radiation 46 that is applied to thesubject 50. Therefore, the first radiographic image capturing apparatus10A of a portable type, which is small in size and weight, can simplyand quickly be readied for capturing radiographic images.

The radiation detector 86 may comprise a light readout type of radiationdetector for acquiring radiographic image information. When radiation isapplied through a subject to solid-state detecting elements of the lightreadout type of radiation detector, the solid-state detecting elementsstore respective electrostatic latent images of the subject depending onthe applied dose of the radiation. For reading the stored electrostaticlatent images, reading light is applied to the radiation detector inorder to cause the solid-state detecting elements to generate currentsthat depend on the stored electrostatic latent images. The generatedcurrents are detected as representative of radiographic imageinformation of the subject. Thereafter, erasing light is applied to theradiation detector in order to erase remaining electrostatic latentimages from the solid-state detecting elements, so that the radiationdetector can be reused. For details, reference should be made toJapanese Laid-Open Patent Publication No. 2000-105297.

The first radiographic image capturing apparatus 10A may comprise awater-resistant, hermetically sealed structure, thereby making the firstradiographic image capturing apparatus 10A resistant to contamination byblood and bacteria. When necessary, the first radiographic imagecapturing apparatus 10A may be cleaned and sterilized for enablingrepetitive use.

The first radiographic image capturing apparatus 10A may performwireless communications with an external device by way of ordinarywireless communications using radio waves, or by way of optical wirelesscommunications using infrared rays or the like.

In the first embodiment, as shown in FIG. 30, the first radiographicimage capturing apparatus 10A may be devoid of the tape measure 72.Without the tape measure 72, the first radiographic image capturingapparatus 10A provides the same advantages offered by components thereofother than the tape measure 72.

As described above, major components of the joining mechanism 82 areprovided in the cassette 12. However, the joining mechanism 82 may beprovided in the radiation source device 18. Such a modification offersthe same advantages as those referred to above.

The first radiographic image capturing apparatus 10A may be modified asdescribed below.

FIG. 31 shows a first radiographic image capturing apparatus 10Aaccording to a modification, in which the unlocking button 34, the hook64, etc., are provided in the radiation source device 18.

As shown in FIG. 31, the side 14 a of the cassette 12 does not includethe aforementioned holders 16 a, 16 b, and the radiation source device18 has a flat side, which faces the side 14 a of the cassette 12.Opposite ends of the radiation source device 18 have respectiveunlocking buttons 34. The radiation source device 18 also has throughholes 62 and hooks 64 provided in the flat side thereof, which faces theside 14 a of the cassette 12, near opposite ends of the radiation sourcedevice 18. Connection terminals 68 a, 68 b are disposed on the flat sideof the radiation source device 18 near one of the ends of the radiationsource device 18.

The side 14 a of the cassette 12 has through holes 66 defined therein,which are in alignment with the respective through holes 62 andconnection terminals 70 a, 70 b, which in turn are in alignment with theconnection terminals 68 a, 68 b.

The first radiographic image capturing apparatus 10A shown in FIG. 31operates in the following manner. While the flat side of the radiationsource device 18 and the side 14 a of the cassette 12 face toward eachother, the hooks 64 are inserted into the respective through holes 66,and the connection terminals 68 a, 68 b and the connection terminals 70a, 70 b are brought into engagement with each other. At this time, theradiation source device 18 and the cassette 12 are integrally joined toeach other.

The first radiographic image capturing apparatus 10A shown in FIG. 31offers the same advantages as the first radiographic image capturingapparatus 10A according to the first embodiment.

According to the modification shown in FIG. 31, since the unlockingbuttons 34 are disposed on opposite ends of the radiation source device18, an operator 38 can easily disconnect the radiation source device 18from the cassette 12, simply by detaching the radiation source device 18from the cassette 12 while pressing the unlocking buttons 34.

In the first embodiment, as shown in FIG. 32, a cradle 180 for chargingthe batteries 308 of the first radiographic image capturing apparatus10A may be positioned at a desired location in the hospital. The cradle180 is not only capable of charging the batteries 308, but may also havea wireless or wired communication function for sending and receivingnecessary information to and from an external device in the hospital.Information sent from the cradle 180 may include radiation imageinformation recorded in the first radiographic image capturing apparatus10A, which is connected to the cradle 180.

The cradle 180 has a display unit 182 for displaying the charged stateof the first radiographic image capturing apparatus 10A, which isconnected to the cradle 180, and other necessary information, includingradiation image information acquired from the first radiographic imagecapturing apparatus 10A.

A plurality of cradles 180 may be connected through a network, andcharged states of respective first radiographic image capturingapparatus 10A, which are connected to the cradles 180, may be retrievedthrough the network, so that the user can confirm the locations of firstradiographic image capturing apparatus 10A that are sufficientlycharged, based on the retrieved charged states.

A radiographic image capturing apparatus 10B according to a secondembodiment of the present invention, which will hereinafter be referredto as a “second radiographic image capturing apparatus 10B,” will bedescribed below with reference to FIGS. 33 through 40.

The second radiographic image capturing apparatus 10B essentially isidentical in structure to the first radiographic image capturingapparatus 10A according to the first embodiment, but differs therefromin that a detecting screen 250 is drawn out slightly from the cassette12 through the side 14 b thereof that is remote from the side 14 a onwhich the holders 16 a, 16 b project, and a weight bar 252 is coupled toa distal end of the detecting screen 250. Among the other sides 14 c, 14d of the cassette 12, side 14 c has the first energy input/output unit300 or the second energy input/output unit 302 (see FIG. 13) forinputting and outputting electric power through a wired or wirelesslink, for example, a USB terminal 28 that serves as an interface meansfor sending and receiving information to and from an external device, acard slot 32 for inserting the memory card 30 therein, and the unlockingbutton 34, to be described later. On an upper surface 254 of thecassette 12, the mobile terminal 42 is mounted, which is detachable fromthe cassette 12 and includes the display unit 36 and the operating unit40, which is operated by the operator 38. The radiation source device 18has an exposure switch 48, which can be operated by the operator 38 inorder to cause the radiation source 44, which shall be descried later,to start emitting radiation 46.

FIGS. 33 and 34 show the second radiographic image capturing apparatus10B in a state of being carried by the operator 38. When the secondradiographic image capturing apparatus 10B is carried by the operator38, the radiation source device 18 and the cassette 12 are joinedintegrally to each other.

When the second radiographic image capturing apparatus 10B is brought toa site, such as a disaster site, a home-care service site, or the like,the second radiographic image capturing apparatus 10B is expanded toresult in the state shown in FIGS. 35 through 40.

As shown in FIG. 39, the upper surface 254 of the cassette 12 has therecess 54, which accommodates the mobile terminal 42 therein. As shownin FIGS. 35 and 37, the cassette 12 houses therein a storage box 256,accommodating therein a roll screen, which constitutes a rolled form ofthe detecting screen 250 and is made of a flexible material permeable toradiation 46. The storage box 256 supports on a side thereof a rotaryencoder 258 for detecting the length by which the detecting screen 250has been reeled out from the storage box 256. The side wall 52 b of thecassette 12, which makes up the side 14 b, has a slot 260 definedtherein, through which the detecting screen 250 can be reeled out fromthe storage box 256.

When the operator 38 pulls the weight bar 252 in a direction away fromthe cassette 12, the detecting screen 250 is drawn or extended out fromthe storage box 256 through the slot 260. At times when the secondradiographic image capturing apparatus 10B is being carried, thedetecting screen 250 is rolled up inside the storage box 256. When thesecond radiographic image capturing apparatus 10B is operated to captureradiographic images, as shown in FIGS. 37, 39 and 40, the detectingscreen 250 is drawn out or extended substantially flatwise underneaththe radiation source device 18 by the operator 38 pulling the weight bar252. The detecting screen 250 has gradations 262 on both side edgesthereof along the direction in which the detecting screen 250 is pulled.

As shown in FIG. 38, the detecting screen 250 houses therein a grid 84for removing scattered rays of radiation 46 from the subject 50 when theradiation source 44 applies radiation 46 to the subject 50, a radiationdetector 86 for detecting radiation 46 that has passed through thesubject 50, and a lead sheet 89 for absorbing back scattered rays ofradiation 46, which are successively arranged in this order from theirradiated surface 20 of the detecting screen 250, i.e., the uppersurface of the detecting screen 250, as shown in FIGS. 37 through 40.The irradiated surface 20 may be constructed as the grid 84. The grid84, the radiation detector 86, and the lead sheet 89 are flexible.

For irradiating the subject 50 with radiation 46 in order to captureradiographic images of the subject 50, a preparatory procedure mustfirst be performed for readying the second radiographic image capturingapparatus 10B for capturing radiographic images. Such a preparatoryprocedure includes a process for presetting a source-to-image distance(SID), which represents an distance (imaging distance) between the focuspoint 122 of the radiation source 44 and a position 124 (see FIG. 38) onthe radiation detector 86 that lies straight below the focus point 122,and a process for bringing the central position 126 of the irradiatedsurface 20 of the detecting screen 250 into alignment with the center ofa range within which the irradiated surface 20 is irradiated withradiation 46.

The preparatory procedure is carried out as follows. As shown in FIGS.37 through 39, while the radiation source device 18 is separated fromthe cassette 12, the operator 38 pulls the ribbon 76 from the tapemeasure 72 until the length of the ribbon 76, which is reeled out fromthe tape measure 72, becomes equal to the reeled-out length 11 dependingon the SID. The laser pointer 104 is controlled by the radiation sourcecontroller 102 in order to apply a laser beam 128 to the irradiatedsurface 20, thereby displaying a crisscross mark 130 on the irradiatedsurface 20, which represents the center of a range within which theirradiated surface 20 is irradiated with radiation 46.

The operator 38 determines the central position of the irradiatedsurface 20 by observing the gradations 262 thereon. The SID, thereeled-out length 11 depending on the SID, and a distance 12 between theposition 124 or the central position 126 and the side 14 a having thehole 80 through which the ribbon 76 is pulled out, are related to eachother according to the equation SID≈(11²−12²)^(1/2).

After the ribbon 76 has been pulled from the tape measure 72 by thereeled-out length 11, the operator 38 adjusts the position of theradiation source device 18 so as to bring the mark 130 displayed on theirradiated surface 20 into alignment with the central position 126.Thereafter, the operator 38 turns on the exposure switch 48 in order toenable the radiation source 44 to apply radiation 46 with respect to thesubject 50 on the irradiated surface 20, thereby capturing radiographicimages of the subject 50, as shown in FIG. 40. In FIG. 40, an example isshown in which a radiographic image of a hand of the subject 50 iscaptured.

The second radiographic image capturing apparatus 10B also operatesaccording to the operation sequences shown in FIGS. 23 through 29. Thesecond radiographic image capturing apparatus 10B is operated accordingto a preparatory procedure and an image capturing process as follows.

First, the operator performs operations to ready the second radiographicimage capturing apparatus 10B for capturing radiographic images at asite where the second radiographic image capturing apparatus 10B hasbeen carried. The operator 38 operates the operating unit 40 of themobile terminal 42 in order to register image capturing conditions,including subject information (e.g., SID) of the subject 50 to beimaged.

The operator 38 pulls the weight bar 252 in order to draw or extend thedetecting screen 250 from the storage box 256 by a given length(drawn-out length 13), which is required to capture radiographic imagesof a body region of the subject 50 to be imaged. The rotary encoder 258detects the drawn-out length 13 of the detecting screen 250, and sends asignal representative of the detected drawn-out length 13 to the SIDdetermining unit 168.

When the unlocking button 34 is pressed by the operator 38, the hook 64and the slide 56 are displaced against the resiliency of the spring 60and along the side wall 52 a toward the side wall 52 d, thereby bringingthe hook 64 out of engagement with the edge of the through hole 66.

While the hook 64 is kept out of engagement with the edge of the throughhole 66, i.e., while the operator 38 presses the unlocking button 34,the operator 38 removes or separates the radiation source device 18 fromthe cassette 12. The connection terminal 68 a becomes disengaged fromthe connection terminal 70 a, and the connection terminal 68 b becomesdisengaged from the connection terminal 70 b, thereby releasing theradiation source device 18 and the cassette 12 from each other. Theoperator 38 sets the imaging distance and brings the mark 130, which isdisplayed on the irradiated surface 20, into alignment with the centralposition 126. Thereafter, the operator 38 places and positions thesubject 50 between the irradiated surface 20 and the radiation sourcedevice 18. The operator 38 moves the radiation source device 18 in orderto reel out the ribbon 76 from the tape measure 72, until the actualreeled-out length of the ribbon 76 reaches the reeled-out length 11depending on the SID.

After having adjusted the position of the radiation source device 18until the mark 130 and the central position 126 are aligned with, eachother, the operator 38 places or positions the subject 50 on theirradiated surface 20, so that the center of a body region of thesubject 50 to be imaged is aligned with the central position 126, i.e.,the position of the mark 130.

After the above positional adjustment has been carried out, theradiation source device 18 is secured to the adjusted position by aholder, not shown, for example.

After the subject 50 is positioned, the operator 38 turns on theexposure switch 48 in order to start capturing radiographic images ofthe subject 50.

The second radiographic image capturing apparatus 10B offers the sameadvantages as the first radiographic image capturing apparatus 10A.

While the second radiographic image capturing apparatus 10B istransported, the radiation source device 18 and the cassette 12 arecoupled to each other integrally by the joining mechanism 82. While thesecond radiographic image capturing apparatus 10B is operated to captureradiographic images, the radiation source device 18 and the cassette 12are separated from each other, and the detecting screen 250 is drawn andextended from the cassette 12. Thereafter, the radiation source 44 ofthe radiation source device 18 emits radiation 46, which is applied tothe subject 50. Therefore, the second radiographic image capturingapparatus 10B of a portable type, which is small in size and weight, cansimply and quickly be readied for capturing radiographic images.

The storage box 256, which is disposed in the cassette 12, accommodatestherein the detecting screen 250 in a rolled-up form, so as to beflexible and capable of being extended in sheet form. When the secondradiographic image capturing apparatus 10B is carried to a site, such asa disaster site, a home-care service site, or the like, the detectingscreen 250 is stored in a rolled-up form inside the storage box 256.When the second radiographic image capturing apparatus 10B is operatedto capture radiographic images, the detecting screen 250 is drawn outfrom the storage box 256 in a flat sheet form. Therefore, the secondradiographic image capturing apparatus 10B is small in overall size.

A portable radiographic image capturing apparatus according to a thirdembodiment of the present invention, which hereinafter will be referredto as a “third radiographic image capturing apparatus 10C,” will bedescribed in detail below with reference to FIGS. 41 through 47.

The third radiographic image capturing apparatus 10C includes theradiation source device 18, the cassette 12, and a personal computer(controller, PC) 280, which is electrically connected to the radiationsource device 16 by a wired or wireless input/output unit, as well asbeing electrically connected to the cassette 12 by a wired or wirelessinput/output unit. Further, the third radiographic image capturingapparatus 10C incorporates therein a digital camera 270 for capturing animage of a predetermined imaging area. The PC 280 can be operated by theoperator 38 (see FIG. 44) of the third radiographic image capturingapparatus 10C. The PC 280 is capable of sending signals to and receivingsignals from a medical organization to which the operator 38 belongs, byway of wireless communications via a network such as a public network orthe like.

The cassette 12 includes the battery unit 304, a battery controller 306,a radiation detector 86, a cassette controller 92, and a transceiver 94,which are identical to those shown in FIG. 11. As shown in FIG. 41, thecassette 12 has a first energy input/output unit 300 and a second energyinput/output unit 302 located on a side wall of the casing. Theradiation source device 18 includes a battery unit 304, a batterycontroller 306, a transceiver 100, a radiation source controller 102 forcontrolling the radiation source 44, and a laser pointer 104, which areidentical to those shown in FIG. 11. A first energy input/output unit300 and a second energy input/output unit 302, which are identical tothose of the cassette 12, are mounted respectively on a side wall and acircumferential wall of the casing of the radiation source device 18, asshown in FIG. 41.

As shown in FIG. 41, the PC 280 comprises a notebook-shaped personalcomputer, including an operating unit 282 such as a keyboard, a mouse,or the like, and a display unit 284. Alternatively, the PC 280 may bereplaced with a mobile phone or a PDA (Personal Digital Assistant).

The PC 280 has a power supply switch, speakers, a microphone, and otheraccessories, similar to those of ordinary notebook-shaped personalcomputers. The PC 280 incorporates therein a transceiver 288 (see FIG.45) for sending information to and receiving information from anexternal device such as a network, the radiation source device 18, thecassette 12, or the like. The PC 280 also includes, on a side wallthereof, a first energy input/output unit 300, and a second energyinput/output unit 302. In FIG. 41, the first energy input/output unit300 of the PC 280 is connected by a cable to the first energyinput/output unit 300 of the radiation source device 18, while thesecond energy input/output unit 302 of the PC 280 is connected by acable to the first energy input/output unit 300 of the cassette 12.However, the first energy input/output unit 300 and the second energyinput/output unit 302 may be connected wirelessly.

As shown in FIG. 45, the PC 280 includes a battery unit 304 and abattery controller 306, which are identical to those of the radiationsource device 18.

FIG. 44 shows the manner in which the third radiographic image capturingapparatus 10C is carried by an operator 38.

When the third radiographic image capturing apparatus 10C is carried bythe operator 38, the radiation source device 18, the cassette 12, andthe folded PC 280 are electrically disconnected and housed in an attachécase 286. The operator 38 can grip a grip 24 of the attaché case 286 andcarry the attaché case 286 from the medical organization to a desiredsite, e.g., a disaster site or a home-care service site. At the sitewhere the attaché case 286 has been carried, the operator 38 can takeout the radiation source device 18, the cassette 12, and the folded PC280 from the attaché case 286, and assemble them into the configurationshown in FIGS. 41 through 43. The operator 38 then can perform apreparatory procedure in order to ready the third radiographic imagecapturing apparatus 10C for capturing radiographic images of a person ata disaster site or a home-care service site.

The third radiographic image capturing apparatus 10C also operatesaccording to the operation sequences shown in FIGS. 23 through 29. Inaccordance with a preparatory procedure, the third radiographic imagecapturing apparatus 10C operates in the following manner.

The operator 38 takes the radiation source device 18, the cassette 12,etc., out of the attaché case 286, and electrically connects theradiation source device 18 and the cassette 12 to the PC 280 in a wiredor wireless fashion. The operator 38 places the PC 280, the radiationsource device 18, and the cassette 12 in the positional relationshipshown in FIGS. 41 through 43.

Then, the operator 38 starts up the PC 280, thereby readying the thirdradiographic image capturing apparatus 10C for capturing radiographicimages. Thereafter, the operator 38 turns on the exposure switch 48 tobegin capturing radiographic images.

In the operation sequences shown in FIGS. 23 through 29, if the distancebetween any two of the devices that incorporate the battery controller306 therein, i.e., the radiation source device 18, the cassette 12, thePC 280, etc., of the third radiographic image capturing apparatus 100,and which belong to the third radiographic image capturing apparatus100, satisfies the certain condition referred to above, then the thirdactivator/deactivator 332C outputs an activation signal. If the distancedoes not satisfy the certain condition after the thirdactivator/deactivator 332C has output the activation signal, then thethird activator/deactivator 332C outputs a full deactivation signal.

More specifically, the third activator/deactivator 332C (see FIG. 17A)according to the first mode outputs an activation signal if the lineardistance between at least two of the radiation source device 18, thecassette 12, and the PC 280 becomes equal to or smaller than the presetreference distance. The third activator/deactivator 332C (see FIG. 17B)according to the second mode outputs an activation signal if the lineardistance between at least two of the radiation source device 18, thecassette 12, and the PC 280 lies within the communication range of eachof the devices. The third activator/deactivator 332C (see FIG. 17C)according to the third mode outputs an activation signal if the lineardistance between at least two of the radiation source device 18, thecassette 12, and the PC 280 lies within a range in which the devices canbe connected in a wired or wireless fashion.

If the distance between the cassette 12 and the radiation source device18, for example, satisfies the certain condition, then the thirdactivator/deactivator 332C outputs an activation signal in the cassette12 and the radiation source device 18. Thereafter, if the distancebetween the cassette 12 and the PC 280 and the distance between theradiation source device 18 and the PC 280 also satisfy the certaincondition, then the third activator/deactivator 332C outputs anactivation signal in the PC 280. Thereafter, only if the PC 280 movesaway, whereby the distance between the cassette 12 and the PC 280 andthe distance between the radiation source device 18 and the PC 280 failto satisfy the certain condition, then the third activator/deactivator332C outputs a full deactivation signal in the PC 280. Although thethird activator/deactivator 332C outputs a full deactivation signal alsoin the cassette 12 and the radiation source device 18, since thedistance between the cassette 12 and the radiation source device 18satisfies the certain condition, the third activator/deactivator 332Cimmediately outputs an activation signal, thus making it possible tosupply electric power.

If the distance between any two of the cassette 12, the radiation sourcedevice 18, and the PC 280 of the third radiographic image capturingapparatus 10C satisfies the certain condition, then since it becomespossible to supply electric power using such devices, it also ispossible to supply electric power between either one of the devices andanother device of another third radiographic image capturing apparatus10C.

For example, if from among the cassette 12, the radiation source device18, and the PC 280 of the third radiographic image capturing apparatus10C that is used to capture radiographic images, the distance betweenthe cassette 12 and the radiation source device 18 satisfies the certaincondition, then it becomes possible to supply electric power between theaforesaid cassette 12 and the aforesaid radiation source device 18 thatare used to capture radiographic images, and also to supply electricpower between the aforesaid cassette 12 and another radiation sourcedevice 18 that is not used to capture radiographic images. It also ispossible to supply electric power between the aforesaid cassette 12 andanother cassette 12 that is not used to capture radiographic images,between the aforesaid radiation source device 18 and another radiationsource device 18 that is not used to capture radiographic images, andbetween the aforesaid radiation source device 18 and another cassette 12that is not used to capture radiographic images.

If from among the cassette 12, the radiation source device 18, and thePC 280 of the third radiographic image capturing apparatus 10C that isused to capture radiographic images, the distance between the cassette12 and the PC 280 satisfies the certain condition, then it is possibleto supply electric power between the aforesaid cassette 12 and the PC280 that are used to capture radiographic images, and also to supplyelectric power between the aforesaid cassette 12 and another radiationsource device 18 that is not used to capture radiographic images. Italso is possible to supply electric power between the aforesaid cassette12 and another cassette 12 that is not used to capture radiographicimages, between the PC 280 and another radiation source device 18 thatis not used to capture radiographic images, and between the PC 280 andanother cassette 12 that is not used to capture radiographic images.

Similarly, if from among the cassette 12, the radiation source device18, and the PC 280 of the third radiographic image capturing apparatus10C that is used to capture radiographic images, the distance betweenthe radiation source device 18 and the PC 280 satisfies the certaincondition, then it is possible to supply electric power between theaforesaid radiation source device 18 and the PC 280 that are used tocapture radiographic images, and also to supply electric power betweenthe aforesaid radiation source device 18 and another radiation sourcedevice 18 that is not used to capture radiographic images. It also ispossible to supply electric power between the aforesaid radiation sourcedevice 18 and another cassette 12 that is not used to captureradiographic images, between the PC 280 and another radiation sourcedevice 18 that is not used to capture radiographic images, and betweenthe PC 280 and another cassette 12 that is not used to captureradiographic images.

If the distances between the cassette 12, the radiation source device18, and the PC 280 of the third radiographic image capturing apparatus10C that is used to capture radiographic images satisfy the certaincondition, then it is possible to supply electric power between theaforesaid cassette 12 and the aforesaid radiation source device 18 viathe PC 280, and also to supply electric power between the aforesaidcassette 12 and another radiation source device 18 that is not used tocapture radiographic images via the PC 280. It also is possible tosupply electric power between the aforesaid cassette 12 and anothercassette 12 that is not used to capture radiographic images via the PC280, between the aforesaid radiation source device 18 and anotherradiation source device 18 that is not used to capture radiographicimages via the PC 280, and between the aforesaid radiation source device18 and another cassette 12 that is not used to capture radiographicimages via the PC 280.

Electric power may be supplied via the PC 280 according to a processthat differs from the process carried out by the first radiographicimage capturing apparatus 10A and the second radiographic imagecapturing apparatus 10B. The different process comprises an electricpower collecting process for collecting all or part of the electricpower stored in the battery 308 of the radiation source device 18, andall or part of the electric power stored in the battery 308 of thecassette 12, for the battery unit 304 of the PC 280.

An electric power collector 420 for carrying out the above electricpower collecting process will be described below with reference to FIGS.46 and 47.

The electric power collector 420 is incorporated in the batterycontroller 306. The electric power collector 420 is activated by anoperation made by the operator 38 in order to instruct collection ofelectric power, e.g., by left-clicking on an icon representingcollection of electric power. As shown in FIG. 46, the electric powercollector 420 comprises the device connection detector 360, an electricpower collection ID acquirer 422, an electric power collectioninformation acquirer 424, an electric power collection supply routesetting unit 426, an electric power collection level setting unit 428,the electric power supply controller 374, the remaining level detector376, an electric power collection remaining level updater 430, and anelectric power collection remaining level information transfer unit 432.

Details of an operation sequence of the electric power collector 420will be described below with reference to FIGS. 46 and 47.

In step S301 shown in FIG. 47, the device connection detector 360detects devices, i.e., the radiation source device 18 and the cassette12, which are connected to the first energy input/output unit 300 andthe second energy input/output unit 302 of the PC 280.

The electric power collection ID acquirer 422 sends a transfer requestto the connected devices for transferring IDs. Based on the transferrequest, the connected devices output IDs thereof to the electric powercollector 420. The electric power collection ID acquirer 422 acquiresthe IDs from the connected devices, and registers the IDs in the memory330 (see FIG. 14) in step S302.

The electric power collection information acquirer 424 acquiresremaining level information tables corresponding to the IDs, and storesthe acquired remaining level information tables in the memory 330 instep S303.

The electric power collection supply route setting unit 426 sets asupply route from the device connected to the first energy input/outputunit 300 to the PC 280, and a supply route from the device connected tothe second energy input/output unit 302 to the PC 280. Based on the setsupply routes, in step S304, the electric power collection supply routesetting unit 426 outputs supply source instruction signals to theelectric power supply controllers 374 of the respective devices.

In step S305, the electric power collection level setting unit 428 setsan electric power collection level using the operating unit 282, e.g., akeyboard or a mouse, of the PC 280. The electric power collection levelrepresents the sum of a first electric power level to be supplied fromthe device connected to the first energy input/output unit 300 to thebattery 308 of the PC 280, and a second electric power level to besupplied from the device connected to the second energy input/outputunit 302 to the battery 308 of the PC 280. The first electric powerlevel and the second electric power level are supplied respectively tothe electric power supply controllers 374 of the respective devices.

Based on the supply source instruction signals, the electric powersupply controllers 374 of the devices control the batteries 308 thereofto output electric power. Further, based on a supply source instructionsignal, the electric power supply controller 374 of the PC 280 controlsthe battery 308 thereof to input electric power in step S306. Theelectric power supply controllers 374 control the batteries 308 tosupply electric power, and to be supplied with electric power, at aconstant charging rate or at a discharging rate based on the remaininglevel sent from the remaining level detector 376. If the level ofelectric power to be supplied is low, then it is possible to charge anddischarge the batteries 308 quickly.

In step S307, the electric power collection remaining level updater 430updates the remaining battery level corresponding to the ID of thedevice that is connected to the first energy input/output unit 300, bysubtracting the first electric power level from the remaining batterylevel. The electric power collection remaining level updater 430 alsoupdates the remaining battery level corresponding to the ID of thedevice that is connected to the second energy input/output unit 302, bysubtracting the second electric power level from the remaining batterylevel.

When the updating process of the electric power collection remaininglevel updater 430 is completed, then in step S308, the electric powercollection remaining level information transfer unit 432 transfers theremaining level information tables via the network to the database ofthe data center for updating.

The electric power collector 420 may be activated by operations made bythe operator 38 on the operating unit 282, for example, regardless oflocation and time. For example, when the third radiographic imagecapturing apparatus 10C is carried into a medical organization, theelectric power collector 420 may be activated in order to collectelectric power in the battery 308 of the PC 280. Then, when the thirdradiographic image capturing apparatus 10C is carried to a site outsideof the medical organization, the radiation source device 18 and thecassette 12, which are used to capture radiographic images, may besupplied with electric power from the PC 280. At this time, the electricpower manager 390 supplies an optimum electric power level for capturingradiographic images to the radiation source device 18 and to thecassette 12. Alternatively, the electric power collector 420 may beactivated at a site outside of the medical organization, so as tocollect into the PC 280 electric power from a radiation source device 18and a cassette 12, which have deteriorated significantly and whichcannot be used to capture radiographic images, and to supply thecollected electric power to the radiation source device 18 and thecassette 12 that currently are being used to capture radiographicimages.

Since the PC 280 can supply electric power to respective devices, it ispossible to set a supply route from the PC 280 to a radiation sourcedevice 18 that is used to capture radiographic images, as well as asupply route from the PC 280 to a cassette 12 that is used to captureradiographic images. It also is possible to set a supply route from thePC 280 as a supply source to the aforesaid radiation source device 18,as well as a supply route from the PC 280 as a supply source to theaforesaid cassette 12. Furthermore, it is possible to set a supply routefrom the aforesaid radiation source device 18 via the PC 280 to theaforesaid cassette 12, as well as a supply route from the aforesaidcassette 12 via the PC 280 to the aforesaid radiation source device 18.

Since electric power can be supplied from the PC 280 to the radiationsource device 18 and the cassette 12, or electric power can be suppliedbetween the radiation source device 18 and the cassette 12 via the PC280, the PC 280 can perform a centralized electric power managementprocess for efficiently supplying electric power between the radiationsource device 18 and the cassette 12. Inasmuch as electric power can becollected from one or more radiation source devices 18 and one or morecassettes 12 into the PC 280, the PC 280 can perform a battery functionthat enables efficient electric power management, so as to avoid powersupply problems such as sudden power supply interruptions at times whenelectric power needs to be supplied to the radiation source device 18and the cassette 12.

In each of the first radiographic image capturing apparatus 10A, thesecond radiographic image capturing apparatus 10B, and the thirdradiographic image capturing apparatus 10C, in order to determinewhether the distance between the radiation source device 18 and thecassette 12, the distance between the radiation source device 18 and thePC 280, the distance between the cassette 12 and the PC 280, ordistances between the radiation source device 18, the cassette 12, andthe PC 280 are equal to or less than the reference distance, theradiation source device 18, the cassette 12, and the PC 280 may containrespective GPS receivers including GPS antennas therein, and suchdistances may be determined from the positions of the radiation sourcedevice 18, the cassette 12, and the PC 280, which are detected based onsignals from the GPS receivers.

Although certain preferred embodiments of the present invention havebeen shown and described in detail, it should be understood that variouschanges and modifications may be made to the embodiments withoutdeparting from the scope of the invention as set forth in the appendedclaims.

For example, the radiation detector 86 may be a radiation detector 600according to a modified example shown in FIGS. 48 and 49. FIG. 48 is across-sectional view schematically illustrating the structure of threepixel units of the radiation detector 600 according to a modifiedexample of the invention.

The radiation detector 600 includes a signal output unit 604, a sensorunit (photoelectric converter) 606, and a scintillator 608 that aresequentially laminated on an insulating substrate 602. The signal outputunit 604 and the sensor unit 606 form a pixel unit. Plural pixel unitsare arranged in a matrix on the substrate 602, such as an array of pixelunits arranged in rows and columns. In each pixel unit, the signaloutput unit 604 and the sensor unit 606 are arranged so as to overlapeach other.

The scintillator 608 is formed on the sensor unit 606 with a transparentinsulating film 610 interposed therebetween, and has a phosphor filmthat converts radiation 46 incident from the upper side (the sideopposite to the substrate 602) into light and emits the light. It ispreferable that the wavelength range of light emitted by thescintillator 608 be a visible light range (wavelength of 360 nm to 830nm). It is more preferable that the wavelength range of light include agreen wavelength range in order to capture a monochromatic image usingthe radiation detector 600.

Specifically, in a case in which imaging is performed using X-rays asradiation 46, it is preferable that the phosphor used for thescintillator 608 include cesium iodide (CsI). It is more preferable touse CsI(Tl) (thallium-added cesium iodide) having an emission spectrumof 420 nm to 700 nm during the emission of X-rays. The emission peakwavelength of CsI(Tl) in the visible light range is 565 nm.

The scintillator 608, for example, may be formed on a vapor depositionsubstrate by vapor deposition of a columnar crystal of CsI(Tl). As such,in a case in which the scintillator 608 is formed by vapor deposition,an Al plate is generally used as the vapor deposition substrate in termsof the transmittance of X-rays and manufacturing costs, but the vapordeposition substrate is not limited to the Al plate. In a case in whichGOS is used as the scintillator 608, GOS may be applied onto the surfaceof a TFT active matrix substrate to form the scintillator 608, withoutusing the vapor deposition substrate. Alternatively, after thescintillator 608 is formed by applying GOS to a resin base, thescintillator 608 may be attached to a TFT active matrix substrate. Inthis case, even if the application of GOS failed, the TFT active matrixsubstrate would not be damaged.

The sensor unit 606 includes an upper electrode 612, a lower electrode614, and a photoelectric conversion film 616 provided between the upperand lower electrodes 612, 614.

The upper electrode 612 needs to make light generated by thescintillator 608 incident on the photoelectric conversion film 616.Therefore, it is preferable that the upper electrode 612 be made of aconductive material that is at least transparent with respect to theemission wavelength of the scintillator 608. Specifically, it ispreferable that the upper electrode 612 be made of a transparentconducting oxide (TCO) having high transmittance with respect to visiblelight and a small resistance value. A metal thin film, such as an Authin film, may be used as the upper electrode 612. However, when thetransmittance increases to 90% or more, the resistance value is likelyto increase. Therefore, it is preferable that the upper electrode 612 bemade of TCO. For example, it is preferable that the upper electrode 612be made of ITO, IZO, AZO, FTO, SnO₂, TiO₂, ZnO₂, etc. It is mostpreferable that the upper electrode 612 be made of ITO in terms of asimple process, low resistance, and transparency. One upper electrode612 may be common to all pixel units, or the upper electrode 612 may bedivided for each pixel unit.

The photoelectric conversion film 616 includes an organic photoconductor(OPC) and absorbs light emitted from the scintillator 608 and generatesa charge corresponding to the absorbed light. When the photoelectricconversion film 616 includes an organic photoconductor (an organicphotoelectric conversion material), it has a narrow absorption spectrumin the visible light range and absorbs little electromagnetic wavesother than the light emitted from the scintillator 608. Therefore, it ispossible to effectively reduce noise generated due to the absorption ofradiation 46 by the photoelectric conversion film 616. For example, thephotoelectric conversion film 616 may include amorphous silicon insteadof an organic photoconductor. When the photoelectric conversion film 616includes amorphous silicon, it has a wide absorption spectrum and canabsorb light emitted from the scintillator 608 efficiently.

It is preferable that the absorption peak wavelength of the organicphotoconductor forming the photoelectric conversion film 616 be close tothe emission peak wavelength of the scintillator 608 in order to mosteffectively absorb light emitted from the scintillator 608. It is idealthat the absorption peak wavelength of the organic photoconductor isequal to the emission peak wavelength of the scintillator 608. However,when the difference between the absorption peak wavelength and theemission peak wavelength is small, it is possible to sufficiently absorblight emitted from the scintillator 608. Specifically, the differencebetween the absorption peak wavelength of the organic photoconductor andthe emission peak wavelength of the scintillator 608 with respect to theradiation 46 is preferably equal to or less than 10 nm and morepreferably, equal to or less than 5 nm.

Examples of the organic photoconductor capable of satisfying theabove-mentioned conditions include a quinacridone-based organic compoundand a phthalocyanine-based organic compound. For example, the absorptionpeak wavelength of quinacridone in the visible light range is 560 nm.Therefore, when quinacridone is used as the organic photoconductor andCsI(Tl) is used as the material forming the scintillator 608, it ispossible to reduce the difference between the peak wavelengths to 5 nmor less and substantially maximize the amount of charge generated by thephotoelectric conversion film 616.

The sensor unit 606 includes an organic layer that is formed bylaminating or mixing, for example, an electromagnetic wave absorptionportion, a photoelectric conversion portion, an electron transportportion, a hole transport portion, an electron blocking portion, a holeblocking portion, a crystallization prevention portion, an electrode,and an interlayer contact improvement portion. It is preferable that theorganic layer include an organic p-type compound (organic p-typesemiconductor) or an organic n-type compound (organic n-typesemiconductor).

The organic p-type semiconductor is a donor-type organic semiconductor(compound) whose representative example is a hole-transport-type organiccompound and means an organic compound which readily donates electrons.Specifically, in a case in which two organic materials are in contactwith each other during use, one organic compound with low ionizationpotential is the organic p-type semiconductor. Therefore, any organiccompound may be used as the donor-type organic compound as long as ithas an electron donating property.

The organic n-type semiconductor is an acceptor-type organicsemiconductor (compound) whose representative example is anelectron-transport-type organic compound and means an organic compoundwhich readily accepts electrons. Specifically, in a case in which twoorganic compounds are in contact with each other during use, one organiccompound with high electron affinity is the organic n-typesemiconductor. Therefore, any organic compound may be used as theacceptor-type organic compound as long as it has an electron acceptingproperty.

Materials applicable to the organic p-type semiconductor and the organicn-type semiconductor and the structure of the photoelectric conversionfilm 616 have been described in detail in Japanese Laid-Open PatentPublication No. 2009-032854 and thus a detailed description thereof willbe omitted. The photoelectric conversion film 616 may include fullereneor carbon nanotubes.

It is preferable that the thickness of the photoelectric conversion film616 be as large as possible in terms of the absorption of light from thescintillator 608. However, when the thickness of the photoelectricconversion film 616 is greater than a predetermined value, the intensityof the electric field of the photoelectric conversion film 616 generatedby the bias voltage applied from both ends of the photoelectricconversion film 616 is reduced, which makes it difficult to collectcharge. Therefore, the thickness of the photoelectric conversion film616 is preferably from 30 nm to 300 nm, more preferably from 50 nm to250 nm, and most preferably from 80 nm to 200 nm.

One photoelectric conversion film 616 is common to all pixel units.However, the photoelectric conversion film 616 may be divided for eachpixel unit. The lower electrode 614 is a thin film that is divided foreach pixel unit. However, one lower electrode 614 may be common to allpixel units. The lower electrode 614 may be appropriately made of atransparent or opaque conductive material, such as aluminum or silver.The thickness of the lower electrode 614 may be, for example, from 30 nmto 300 nm.

In the sensor unit 606, a predetermined bias voltage can be appliedbetween the upper electrode 612 and the lower electrode 614 to move oneof the charges (a hole and an electron) generated from the photoelectricconversion film 616 to the upper electrode 612 and move the other chargeto the lower electrode 614. In the radiation detector 600 according tothis modified example, a wiring line is connected to the upper electrode612 and the bias voltage is applied to the upper electrode 612 throughthe wiring line. It is assumed that the polarity of the bias voltage isdetermined such that the electron generated in the photoelectricconversion film 616 is moved to the upper electrode 612 and the hole ismoved to the lower electrode 614. However, the polarity may be reversed.

The sensor unit 606 forming each pixel unit may include at least thelower electrode 614, the photoelectric conversion film 616, and theupper electrode 612. In order to prevent an increase in dark current, itis preferable that at least one of electron blocking film 618 and holeblocking film 620 be provided, and it is more preferable that both theelectron blocking film 618 and the hole blocking film 620 be provided.

The electron blocking film 618 may be provided between the lowerelectrode 614 and the photoelectric conversion film 616. In a case inwhich the bias voltage is applied between the lower electrode 614 andthe upper electrode 612, it is possible to prevent an increase in thedark current due to the injection of electrons from the lower electrode614 into the photoelectric conversion film 616.

The electron blocking film 618 may be made of an electron donatingorganic material. In practice, the material used for the electronblocking film 618 may be selected according to a material forming anadjacent electrode and a material forming an adjacent photoelectricconversion film 616. It is preferable that the material used for theelectron blocking film 618 have an electron affinity (Ea) that is atleast 1.3 eV higher than the work function (Wf) of the material formingthe adjacent electrode and have an ionization potential (Ip) equal to orless than that of the material forming the adjacent photoelectricconversion film 616. Materials applicable as the electron donatingorganic material have been described in detail in Japanese Laid-OpenPatent Publication No. 2009-032854 and thus a detailed descriptionthereof will be omitted.

The thickness of the electron blocking film 618 is preferably from 10 nmto 200 nm, more preferably from 30 nm to 150 nm, and most preferablyfrom 50 nm to 100 nm in order to reliably obtain the effect ofpreventing the dark current and prevent a reduction in the photoelectricconversion efficiency of the sensor unit 606.

The hole blocking film 620 may be provided between the photoelectricconversion film 616 and the upper electrode 612. In a case in which thebias voltage is applied between the lower electrode 614 and the upperelectrode 612, it is possible to prevent an increase in the dark currentdue to the injection of holes from the upper electrode 612 into thephotoelectric conversion film 616.

The hole blocking film 620 may be made of an electron accepting organicmaterial. The thickness of the hole blocking film 620 is preferably from10 nm to 200 nm, more preferably from 30 nm to 150 nm, and mostpreferably from 50 nm to 100 nm in order to reliably obtain the effectof preventing the dark current and prevent a reduction in thephotoelectric conversion efficiency of the sensor unit 606.

In practice, the material used for the hole blocking film 620 may beselected according to a material forming an adjacent electrode and amaterial forming an adjacent photoelectric conversion film 616. It ispreferable that the material used for the hole blocking film 620 have anionization potential (Ip) that is at least 1.3 eV higher than the workfunction (Wf) of the material forming the adjacent electrode and have anelectron affinity (Ea) equal to or more than that of the materialforming the adjacent photoelectric conversion film 616. Materialsapplicable as the electron accepting organic material have beendescribed in detail in Japanese Laid-Open Patent Publication No.2009-032854 and thus a detailed description thereof will be omitted.

In a case in which the bias voltage is set such that, among the chargesgenerated in the photoelectric conversion film 616, holes are moved tothe upper electrode 612 and electrons are moved to the lower electrode614, the positions of the electron blocking film 618 and the holeblocking film 620 may be reversed. In addition, it is not necessary toprovide both the electron blocking film 618 and the hole blocking film620. When either the electron blocking film 618 or the hole blockingfilm 620 is provided, it is possible to a certain extent to obtain theeffect of preventing the dark current.

As shown in FIG. 49, the signal output unit 604 is provided on thesurface of the substrate 602 so as to correspond to the lower electrode614 of each pixel unit. The signal output unit 604 has a storagecapacitor 622 that stores the charge moved to the lower electrode 614,and a TFT 624 that converts the charge stored in the storage capacitor622 into an electric signal and outputs the electric signal. A region inwhich the storage capacitor 622 and the TFT 624 are formed has a portionthat overlaps the lower electrode 614 in a plan view. In this way, thesignal output unit 604 and the sensor unit 606 in each pixel unitoverlap each other in the thickness direction. It is possible tominimize the plane area of the radiation detector 600 (pixel unit), whenthe signal output unit 604 is formed such that the storage capacitor 622and the TFT 624 are completely covered with the lower electrode 614.

The storage capacitor 622 is electrically connected to the correspondinglower electrode 614 through a conductive line that is formed so as topass through an insulating film 626 provided between the substrate 602and the lower electrode 614. In this way, it is possible to move thecharge captured by the lower electrode 614 to the storage capacitor 622.

The TFT 624 is formed by laminating a gate electrode 628, a gateinsulating film 630, and an active layer (channel layer) 632 andproviding a source electrode 634 and a drain electrode 636 on the activelayer 632 with a predetermined gap therebetween. The active layer 632may be made of, for example, amorphous silicon, an amorphous oxide, anorganic semiconductor material, or carbon nanotubes. The materialforming the active layer 632 is not limited thereto.

An oxide (for example, an In—O-based oxide) including at least one ofIn, Ga, and Zn is preferable as the amorphous oxide that can form theactive layer 632. An oxide (for example, an In—Zn—O-based oxide, anIn—Ga—O-based oxide, or a Ga—Zn—O-based oxide) including at least two ofIn, Ga, and Zn is more preferable as the amorphous oxide. An oxideincluding In, Ga, and Zn is most preferable as the amorphous oxide. Asan In—Ga—Zn—O-based amorphous oxide, an amorphous oxide having acomposition represented by InGaO₃(ZnO)_(m) (m is a natural numbersmaller than 6) in a crystalline state is preferable, and InGaZnO₄ ismore preferable. The amorphous oxide that can form the active layer 632is not limited thereto.

A phthalocyanine compound, pentacene, or vanadyl phthalocyanine may begiven as an example of the organic semiconductor material that can formthe active layer 632, but the organic semiconductor material is notlimited thereto. The structure of the phthalocyanine compound has beendescribed in detail in Japanese Laid-Open Patent Publication No.2009-212389 and thus a detailed description thereof will be omitted.

When the active layer 632 of the TFT 624 is made of an amorphous oxide,an organic semiconductor material, or carbon nanotubes, radiation 46,such as X-rays, is not absorbed. Even if the radiation 46 is absorbed,the absorbed amount will be very small. Therefore, it is possible toeffectively prevent the generation of noise in the signal output unit604.

In a case in which the active layer 632 is made of carbon nanotubes, itis possible to improve the switching speed of the TFT 624 and form theTFT 624 with low light absorptance in the visible light range. Inaddition, in a case in which the active layer 632 is made of carbonnanotubes, even though a very small amount of metallic impurities ismixed with the active layer 632, the performance of the TFT 624 issignificantly reduced. Therefore, it is necessary to separate andextract carbon nanotubes with very high purity using, for example,centrifugal separation and form the active layer 632 with the carbonnanotubes.

All of the amorphous oxide, the organic semiconductor material, thecarbon nanotubes, and the organic photoconductor can be used to form afilm at a low temperature. Thus, the substrate 602 is not limited to asubstrate with high heat resistance, such as a semiconductor substrate,a quartz substrate, or a glass substrate, but a flexible substrate, suchas a plastic substrate, an aramid substrate, or a bio-nanofibersubstrate may be used as the substrate 602. Specifically, for example, aflexible substrate made of the following materials may be used:polyester, such as polyethylene terephthalate, polybutylene phthalate,or polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, andpolychlorotrifluoroethylene. When such a flexible substrate made ofplastic is used, it is possible to reduce the weight of the substrate.For example, this structure has an advantage in portability.

When the photoelectric conversion film 616 is formed of the organicphotoconductor and the TFT 624 is formed of the organic semiconductormaterial, it is possible to form films of the photoelectric conversionfilm 616 and the TFT 624 at a low temperature with respect to a flexiblesubstrate (substrate 602) of plastic. Also, it is possible to reduce thethickness and weight of the radiation detector 600 in its entirety, andthereby it is possible to reduce the thickness and weight of thecassette 12 housing the radiation detector 600. Accordingly, it ispossible to improve convenience when used outside of a hospital.Further, a base material of the photoelectric conversion unit is made ofa flexible material instead of glass that is commonly used. Thus, it ispossible to enhance resistance to damage or the like when theradiographic image capturing apparatus is carried or used.

In addition, for example, an insulating layer for ensuring an insulatingproperty, a gas barrier layer for preventing the penetration of water oroxygen, and an undercoating layer for improving flatness or the adhesionof, for example, the electrode may be provided on the substrate 602.

Since aramid can be applied to a high-temperature process of 200 degreesor more, a transparent electrode material can be cured at a hightemperature to have low resistance, and the aramid can respond to theautomatic mounting of a driver IC including a solder reflow process. Inaddition, the thermal expansion coefficient of aramid is close to thatof ITO (indium tin oxide) or a glass substrate. Therefore, after anaramid substrate is manufactured, the warping of the aramid substrate issmall and the aramid substrate is less likely to be cracked. Inaddition, aramid is capable of forming a substrate thinner than, forexample, a glass substrate. Aramid may be laminated on a super-thinglass substrate to form the substrate 602.

The bio-nanofiber is a composite of a cellulose microfibril bundle(bacterial cellulose) generated by bacteria (Acetobacter, AcetobacterXylinum) and a transparent resin. The cellulose microfibril bundle has awidth of 50 nm, a size of one-tenth of the visible light wavelength,high strength, high elasticity, and a low thermal expansion coefficient.A transparent resin, such as an acrylic resin or an epoxy resin, isimpregnated into the bacterial cellulose and is then cured to obtainbio-nanofiber that has a light transmittance of about 90% at awavelength of 500 nm while including 60 to 70% of fiber. Thebio-nanofiber has a low thermal expansion coefficient (3 to 7 ppm) equalto that of a silicon crystal, strength (460 MPa) similar to that ofsteel, high elasticity (30 GPa), and flexibility. Therefore, thebio-nanofiber is capable of forming a substrate 602 thinner than, forexample, a glass substrate.

In this example, the signal output unit 604, the sensor unit 606, andthe transparent insulating film 610 are sequentially formed on thesubstrate 602 and the scintillator 608 is bonded to the substrate 602 byan adhesive resin with low light absorptance, thereby forming theradiation detector 600.

In the radiation detector 600 according to the modified example, sincethe photoelectric conversion film 616 is made of an organicphotoconductor and the active layer 632 of the TFT 624 is made of theorganic semiconductor material, radiation 46 is hardly absorbed by thephotoelectric conversion film 616 or the signal output unit 604.Therefore, it is possible to prevent a reduction in sensitivity for theradiation 46.

Both the organic semiconductor material forming the active layer 632 ofthe TFT 624 and the organic photoconductor forming the photoelectricconversion film 616 can be used to form a film at a low temperature.Therefore, the substrate 602 can be made of a plastic resin, aramid, orbio-nanofiber that absorbs a small amount of radiation 46. Accordingly,it is possible to prevent a reduction in sensitivity for the radiation46.

For example, in a case in which the radiation detector 600 is adhered tothe irradiated surface 20 of the housing and the substrate 602 is madeof a plastic resin with high rigidity, aramid, or bio-nanofiber, it ispossible to reduce the thickness of the irradiated surface 20 of thehousing since the radiation detector 600 has high rigidity. In addition,in a case in which the substrate 602 is made of a plastic resin, aramid,or bio-nanofiber having high rigidity, the radiation detector 600 hasflexibility. In case the substrate 602 is made of a plastic resin,aramid, or bio-nanofiber having high rigidity, even when an impact isapplied to the irradiated surface 20, the radiation detector 600 is lesslikely to be damaged due to its flexibility.

The radiation detector 600 according to the modified example is aso-called rear surface reading type (so-called PSS (Penetration SideSampling) type) in which the light emitted from the scintillator 608 isconverted by the sensor unit 606 (photoelectric conversion film 616)into the electric charge for reading the radiographic image, while thesensor unit 606 is positioned on the side opposite to the radiationsource 44. The type of the radiation detector, however, is not limitedthereto.

For example, a radiation detector may be a so-called front surfacereading type (so-called ISS (Irradiation Side Sampling) type). In thiscase, the insulating substrate 602, the signal output unit 604, thesensor unit 606, and the scintillator 608 are successively laminatedalong an irradiation direction of the radiation 46. The light emittedfrom the scintillator 608 is converted by the sensor unit 606 into theelectric charge for reading the radiographic image, while the sensorunit 606 is positioned on the same side as the radiation source 44.Usually, the scintillator 608 emits light having higher intensity on aradiation-irradiated side by the radiation 46 than a back side.Therefore, in the radiation detector of the front surface reading type,the distance from the scintillator 608 to the photoelectric conversionfilm 616, by which emitted light travels, can be shorter than in theradiation detector 600 of the rear surface reading type. Thus, it ispossible to reduce the diffusion or attenuation of the light. As aresult, the resolution of the radiographic image can be higher.

1. A radiographic image capturing apparatus comprising: a radiationsource device including a radiation source for outputting radiation; anda detector device including a radiation detector for detecting radiationthat is transmitted through a subject when the subject is irradiatedwith radiation by the radiation source, and converting the detectedradiation into a radiographic image; at least one of the radiationsource device and the detector device having an electric power supplylimiting unit for limiting supply of electric power; the electric powersupply limiting unit comprising: an activator/deactivator fordetermining activation or deactivation of supply of electric powerbetween the radiation source device and the detector device, based on apresent position of a corresponding one of the radiation source deviceand the detector device, or based on a distance between the radiationsource device and the detector device; and an electric power supplyactivator for enabling supply of electric power between the radiationsource device and the detector device, if the activator/deactivatordetermines activation of supply of electric power between the radiationsource device and the detector device.
 2. The radiographic imagecapturing apparatus according to claim 1, wherein theactivator/deactivator comprises: a present position acquirer foracquiring the present position of the corresponding one of the radiationsource device and the detector device; and a determiner for determiningwhether or not the acquired present position is outside of a medicalorganization, wherein the electric power supply activator enables supplyof electric power between the radiation source device and the detectordevice, if the determiner judges that the acquired present position isoutside of the medical organization.
 3. The radiographic image capturingapparatus according to claim 2, wherein respective electric power supplylimiting units are provided, respectively, in each of the radiationsource device and the detector device, and the electric power supplyactivators of the electric power supply limiting units enable supply ofelectric power between the radiation source device and the detectordevice, if the determiner judges that the acquired present position isoutside of the medical organization.
 4. The radiographic image capturingapparatus according to claim 2, wherein the activator/deactivatordeactivates supply of electric power between the radiation source deviceand the detector device, if the determiner judges that the acquiredpresent position is within the medical organization.
 5. The radiographicimage capturing apparatus according to claim 1, wherein theactivator/deactivator comprises: a present position acquirer foracquiring the present position of the corresponding one of the radiationsource device and the detector device; and a determiner for determiningwhether or not the acquired present position is in a preset location,wherein the electric power supply activator enables supply of electricpower between the radiation source device and the detector device, ifthe determiner judges that the acquired present position is in thepreset location.
 6. The radiographic image capturing apparatus accordingto claim 5, wherein respective electric power supply limiting units areprovided, respectively, in the radiation source device and the detectordevice, and the electric power supply activators of the electric powersupply limiting units enable supply of electric power between theradiation source device and the detector device, if the determinerjudges that the acquired present position is in the preset location. 7.The radiographic image capturing apparatus according to claim 5, whereinthe activator/deactivator deactivates supply of electric power betweenthe radiation source device and the detector device, if the determinerjudges that the acquired present position is not in the preset location.8. The radiographic image capturing apparatus according to claim 1,wherein the activator/deactivator comprises: a determiner fordetermining whether or not the distance between the radiation sourcedevice and the detector device satisfies a certain condition, whereinthe electric power supply activator enables supply of electric powerbetween the radiation source device and the detector device, if thedeterminer judges that the distance satisfies the certain condition. 9.The radiographic image capturing apparatus according to claim 8, whereinthe activator/deactivator deactivates supply of electric power betweenthe radiation source device and the detector device, if the determinerjudges that the distance does not satisfy the certain condition.
 10. Theradiographic image capturing apparatus according to claim 8, wherein thecertain condition is that the linear distance between the radiationsource device and the detector device is equal to or less than a presetreference distance.
 11. The radiographic image capturing apparatusaccording to claim 8, further comprising: a controller for controllingat least the radiation source device and the detector device, whereinthe determiner determines whether or not the distance between at leasttwo of the radiation source device, the detector device, and thecontroller satisfies the certain condition, and the electric powersupply activator enables supply of electric power between the at leasttwo of the radiation source device, the detector device, and thecontroller, if the determiner judges that the distance satisfies thecertain condition.
 12. The radiographic image capturing apparatusaccording to claim 11, wherein the activator/deactivator deactivatessupply of electric power between the at least two of the radiationsource device, the detector device, and the controller, if thedeterminer judges that the distance does not satisfy the certaincondition.
 13. The radiographic image capturing apparatus according toclaim 11, wherein the certain condition is that the linear distancebetween the at least two of the radiation source device, the detectordevice, and the controller is equal to or less than a preset referencedistance.
 14. The radiographic image capturing apparatus according toclaim 1, wherein the electric power supply limiting unit furthercomprises an electric power controller activatable by the electric powersupply activator based on an electric power supply request, forsupplying electric power only along a route from the radiation sourcedevice to the detector device.
 15. The radiographic image capturingapparatus according to claim 14, wherein the electric power controllersupplies electric power from an electric power storage unit of theradiation source device to an electric power storage unit of thedetector device.
 16. The radiographic image capturing apparatusaccording to claim 15, wherein the electric power storage unit of theradiation source device comprises a battery for supplying electric powerto the radiation source; and the electric power storage unit of thedetector device comprises a built-in capacitor for supplying electricpower to the radiation detector.
 17. The radiographic image capturingapparatus according to claim 1, wherein the electric power supplylimiting unit further comprises: an electric power controlleractivatable by the electric power supply activator based on an electricpower supply request, for supplying electric power only along a routefrom the detector device to the radiation source device.
 18. Theradiographic image capturing apparatus according to claim 17, whereinthe electric power controller supplies electric power from an electricpower storage unit of the detector device to an electric power storageunit of the radiation source device.
 19. The radiographic imagecapturing apparatus according to claim 18, wherein the electric powerstorage unit of the radiation source device comprises a built-incapacitor for supplying electric power to the radiation source; and theelectric power storage unit of the detector device comprises a batteryfor supplying electric power to the radiation detector.
 20. Theradiographic image capturing apparatus according to claim 1, wherein theelectric power supply limiting unit further comprises: an electric powercontroller activatable by the electric power supply activator; theelectric power controller including an electric power manager formanaging electric power required to capture a given number ofradiographic images, and supplying required electric power flexibly toat least one of the radiation source device and the detector device,wherein the electric power manager supplies electric power from one ofthe radiation source device and the detector device, which has excessiveelectric power with respect to the required electric power, to the otherof the radiation source device and the detector device, which hasinsufficient electric power with respect to the required electric power,up to the required electric power.
 21. The radiographic image capturingapparatus according to claim 1, wherein the electric power supplylimiting unit further comprises an electric power controller activatableby the electric power supply activator based on an electric power supplyrequest made before an image capturing process, for supplying electricpower between the radiation source device and the detector device. 22.The radiographic image capturing apparatus according to claim 21,wherein the electric power controller deactivates supply of electricpower between the radiation source device and the detector device from astart of the image capturing process after electric power has beensupplied and until an electric power supply request is given before anext image capturing process.
 23. The radiographic image capturingapparatus according to claim 1, wherein the electric power supplylimiting unit further comprises an electric power controller forsupplying electric power between the radiation source device and thedetector device; and an electric power supply limiter for limitingsupply of the electric power by the electric power controller betweenthe radiation source device and the detector device, during a period inwhich the radiographic image is being captured based on the radiation.24. The radiographic image capturing apparatus according to claim 1,wherein the electric power supply limiting unit further comprises anelectric power controller activatable by the electric power supplyactivator upon completion of an image capturing process, for supplyingelectric power between the radiation source device and the detectordevice.
 25. The radiographic image capturing apparatus according toclaim 1, further comprising: a controller for controlling at least theradiation source device and the detector device; the radiation sourcedevice including a first battery for supplying electric power to theradiation source; the detector device including a second battery forsupplying electric power to the radiation detector; the controllerincluding a third battery and an electric power supply limiting unit,which functions the same as the first-mentioned electric power supplylimiting unit, wherein the electric power supply activator of theelectric power supply limiting unit of at least the controller enablessupply of electric power between the first battery, the second battery,and the third battery, if the activator/deactivator of the electricpower supply limiting unit determines activation of supply of electricpower between the radiation source device and the detector device. 26.The radiographic image capturing apparatus according to claim 25,wherein the electric power supply limiting unit of the controllerincludes an electric power controller activatable by the electric powersupply activator based on an electric power supply request made beforean image capturing process or upon completion of the image capturingprocess, for supplying electric power from the third battery to thefirst battery.
 27. The radiographic image capturing apparatus accordingto claim 25, wherein the electric power supply limiting unit of thecontroller includes an electric power controller activatable by theelectric power supply activator based on an electric power supplyrequest made before an image capturing process or upon completion of theimage capturing process, for supplying electric power from the thirdbattery to the second battery.
 28. The radiographic image capturingapparatus according to claim 26, wherein the controller includes anelectric power collector for collecting electric power from at least oneof the first battery and the second battery into the third battery. 29.The radiographic image capturing apparatus according to claim 1, theradiation detector comprising: a photoelectric converter for absorbinglight converted by a scintillator and generating a charge correspondingto the absorbed light; and a signal output unit for outputting anelectric signal that corresponds to radiographic image information, forthe charge generated by the photoelectric converter, wherein thephotoelectric converter includes an organic photoconductor, and thesignal output unit includes a channel layer that comprises an organicsemiconductor material.
 30. A radiographic image capturing systemcomprising: a radiation source device including a radiation source foroutputting radiation; a detector device including a radiation detectorfor detecting radiation that is transmitted through a subject when thesubject is irradiated with radiation by the radiation source, andconverting the detected radiation into a radiographic image; anactivator/deactivator for determining activation or deactivation ofsupply of electric power between the radiation source device and thedetector device, based on a present position of at least one of theradiation source device and the detector device, or based on a distancebetween the radiation source device and the detector device; and anelectric power supply activator for enabling supply of electric powerbetween the radiation source device and the detector device, if theactivator/deactivator determines activation of supply of electric powerbetween the radiation source device and the detector device.